Devices and systems for docking a heart valve

ABSTRACT

An expandable stent for implantation in a right ventricular outflow tract includes a frame having a waist portion that expands to a deployed size having a first diameter, first and second sealing portions extending in opposite directions from the waist portion and expanding radially outward of the waist portion. The first and second sealing portions are sized to seal against first and second portions of the inner surface of the right ventricular outflow tract at the deployed position over a range of sizes of expansion larger than the first diameter. A band is secured to the waist portion of the frame, restricting expansion of the waist portion substantially beyond the first diameter, such that the waist portion is configured to be spaced apart from the inner surface of the right ventricular outflow tract at the deployed position.

RELATED APPLICATIONS

The present application is a continuation of U.S. patent applicationSer. No. 17/456,523, filed on Nov. 24, 2021, which is a continuation ofU.S. patent application Ser. No. 16/290,628, filed on Mar. 1, 2019, nowU.S. Pat. No. 11,191,638, issued on Dec. 7, 2021, which is acontinuation of U.S. patent application Ser. No. 15/422,354, filed onFeb. 1, 2017, now U.S. Pat. No. 10,363,130, issued on Jul. 30, 2019,which claims the benefit of U.S. provisional application Ser. No.62/292,142, filed on Feb. 5, 2016. Each of the foregoing applications isincorporated herein by reference in its entirety.

FIELD OF THE INVENTION

The present invention relates to heart valves and, in particular,docking stations/stents, delivery systems, and methods for use inimplanting a heart valve, e.g., a transcatheter heart valve (“THV”).

BACKGROUND OF THE INVENTION

Prosthetic heart valves can be used to treat cardiac valvular disorders.The native heart valves (the aortic, pulmonary, tricuspid and mitralvalves) serve critical functions in assuring the forward flow of anadequate supply of blood through the cardiovascular system. These heartvalves can be rendered less effective by congenital, inflammatory, orinfectious conditions. Such conditions can eventually lead to seriouscardiovascular compromise or death. For many years the definitivetreatment for such disorders was the surgical repair or replacement ofthe valve during open heart surgery.

A transcatheter technique can also be used for introducing andimplanting a prosthetic heart valve using a flexible catheter in amanner that is less invasive than open heart surgery. In this technique,a prosthetic valve can be mounted in a crimped state on the end portionof a flexible catheter and advanced through a blood vessel of thepatient until the valve reaches the implantation site. The valve at thecatheter tip can then be expanded to its functional size at the site ofthe defective native valve, such as by inflating a balloon on which thevalve is mounted. Alternatively, the valve can have a resilient,self-expanding stent or frame that expands the valve to its functionalsize when it is advanced from a delivery sheath at the distal end of thecatheter.

Transcatheter heart valves (THVs) may be appropriately sized to beplaced inside most native aortic valves. However, with larger nativevalves, blood vessels, and grafts, aortic transcatheter valves might betoo small to secure into the larger implantation or deployment site. Inthis case, the transcatheter valve may not be large enough tosufficiently expand inside the native valve or other implantation ordeployment site to be secured in place.

Replacing the pulmonary valve, which is sometimes referred to as thepulmonic valve, presents significant challenges. The geometry of thepulmonary artery can vary greatly from patient to patient. Typically,the pulmonary artery outflow tract after corrective surgery is too widefor effective placement of a prosthetic heart valve.

SUMMARY

This summary is meant to provide examples and is not intended to belimiting of the scope of the invention in any way. For example, anyfeature included in an example of this summary is not required by theclaims, unless the claims explicitly recite the feature. The descriptiondiscloses exemplary embodiments of expandable docking stations for anexpandable valve, catheters for the expandable docking stations, andhandles for the catheters. The docking stations, catheters, and handlescan be constructed in a variety of ways.

In one embodiment, for example, a docking station can include a valveseat, one or more sealing portions, and one or more retaining portions.In one embodiment, the valve seat can be substantially unexpandablebeyond a deployed size, i.e., the diameter of the valve seat may only beable to increase a maximum of 0-4 mm. The one or more sealing portionscan be connected to the valve seat and extend radially outward of thevalve seat. The one or more sealing portions can be constructed toexpand and extend outward of the valve seat and provide a seal over arange of sizes (e.g., over a range of sizes of expansion and/or over arange of sizes within the circulatory system or vasculature, forexample, it may be able to provide a seal when expanding in differentblood vessels or locations of a variety of shapes and sizes). The one ormore retaining portions can be connected to the one or more sealingportions. The one or more retaining portions can be configured to retainthe docking station at a deployed position. The expandable dockingstation can expand and provide a seal over a range from 27 mm to 38 mm.The expandable docking station can expand radially outwardly to varyingdegrees along its length L. The valve seat and the one or more sealingportions can act as an isolator that reduces or prevents radial outwardforces of an expandable valve in the valve seat from being transferredto the one or more sealing portions or the one or more retainingportions. The docking station can be configured such that pressure ofblood enhances the retention by the retaining portions. The one or moreretaining portions can be configured such that force applied by at leastone of the one or more retaining portions at the deployed position is inproportion to the pressure of blood acting on the docking station. Theone or more retaining portions can be configured such that force appliedby at least one of the one or more retaining portions is greater whenthe heart is in a diastolic phase than when the heart is in the systolicphase. The valve seat can be formed by a suture, ring, band, structuralarrangement, material, foam, and in other ways. The sealing portion cancomprise a portion of a metal frame covered with a fabric, polymer,and/or other material. The sealing portion can comprise an open cellfoam. A portion of the docking station can be permeable to blood and aportion of the docking station can be impermeable to blood. A portion ofthe docking station that is impermeable to blood can extend from atleast the valve seat to at least the sealing portion. The dockingstation can be adjustable in length. The docking station can include afirst half that a second half of the docking station can adjustablyextend into to adjust the length. The one or more retaining portions canextend radially outward of the one or more sealing portions when thedocking station is in an unconstrained state. Other features describedelsewhere in this disclosure may also be included.

In one exemplary embodiment, a system can include an expandable dockingstation and an expandable valve. The expandable docking station caninclude a valve seat, one or more sealing portions, and one or moreretaining portions. The valve seat can expand to a deployed size. Theone or more sealing portions can be connected to the valve seat and canbe constructed to expand and extend radially outward of the valve seatand provide a seal over a range of sizes of expansion. The one or moreretaining portions can be connected to the one or more sealing portions.The one or more retaining portions can be configured to retain thedocking station at a deployed position. The expandable valve can includean expandable frame and a valve element. The expandable frame can beexpanded to engage the valve seat of the docking station. The valveelement can be connected to the expandable frame. The expandable dockingstation and expandable valve can be configured such that, when implantedin a portion of a circulatory system, a radial outward force applied bythe sealing portions to the portion of the circulatory system, whensealing portions are within the range of sizes, is less than ½ (and canbe less than ⅓, less than ¼, less than ⅛, or less than 1/10) of a radialoutward force applied by the expandable frame to the valve seat. Theexpandable docking station can be configured such that, when implantedin the portion of the circulatory system, the diameter of the valve seatis not increased more than 3M (or not more than 1 mm, 2 mm, or 4 mm) bythe radial outward force applied by the expandable frame to the valveseat. The range of sizes of the sealing portions can be from 27 mm to 38mm. The expandable docking station can be configured to expand radiallyoutwardly to varying degrees along its length L when implanted in theportion of the circulatory system.

The expandable docking station can be configured such that, whenimplanted in the portion of the circulatory system, pressure of blood onthe expandable docking station enhances retention by the retainingportions. The expandable docking station can be configured such thatforce applied by the retaining portions, when implanted in the portionof the circulatory system, is in proportion to the pressure of bloodacting on the assembly. The expandable docking station can be configuredsuch that force applied by the retaining portions, when implanted in theportion of the circulatory system, is greater when the heart is in adiastolic phase than when the heart is in the systolic phase. The valveseat can be formed by a suture, ring, band, structural arrangement,material, foam, and in other ways. The sealing portion can comprise aportion of a metal frame covered with a fabric. The sealing portion cancomprise an open cell foam. A portion of the docking station can bepermeable to blood and a portion of the docking station can beimpermeable to blood. A portion of the docking station that isimpermeable to blood can extends from at least the valve seat to atleast the sealing portion. The docking station can have an overalllength that is adjustable. The docking station can include a first half(i.e., portion) that a second half (i.e., portion) of the dockingstation can adjustably extend into to adjust the overall length. Inother words, the length of the docking station can be adjusted by movingthe second half/portion relative to the first half/portion, and thefirst half/portion may be moved independently from the secondhalf/portion (e.g., one half/portion may remain in place while the otherhalf/portion moves). If one of the first or second halves/portionsextends inside the other half/portion and overlaps to adjust the length,the first half/portion and second half/portion may be adjusted to changethe amount/length of overlap between the two. The one or more retainingportions can extend radially outward of the one or more sealing portionwhen the docking station is in an unconstrained state. Other featuresdescribed elsewhere in this disclosure may also be included.

In one exemplary embodiment, a method can include expanding a dockingstation and expanding a valve in the docking station. The dockingstation can be expanded such that a valve seat of the docking stationexpands to a valve seat deployed size and a sealing portion expands to asealing size that is within a range of sealing sizes. A frame of anexpandable valve can be expanded to engage the valve seat of the dockingstation. A radial outward force applied by the sealing portions over therange of sealing sizes can be less than ½ (and can be less than ⅓, lessthan ¼, less than ⅛, or less than 1/10) of a radial outward forceapplied by the expandable frame to the valve seat after expanding theframe. The valve seat of the docking station can be configured such thata diameter of the valve seat is not increased more than 2 mm (or notmore than 1 mm, 3 mm, or 4 mm) by the radial outward force applied bythe expandable frame to the valve seat. The range of sealing sizes ofthe docking station can be from 27 mm to 38 mm. The valve seat can beformed by a suture, ring, band, structural arrangement, material, foam,and in other ways. Other features/steps described elsewhere in thisdisclosure may also be included.

In one exemplary embodiment a system can include an expandable dockingstation and an expandable valve. The expandable docking station caninclude a valve seat, one or more sealing portions, and one or moreretaining portions. The valve seat can expand to a deployed size. Theone or more sealing portions can be connected to the valve seat and canextend radially outward of the valve seat. The one or more sealingportions can be constructed to expand outward of the valve seat andprovide a seal over a range of sizes. The one or more retaining portionscan be connected to the one or more sealing portions. The one or moreretaining portions can be configured to retain the docking station at adeployed position. The expandable valve can comprise an expandable frameand a valve element. The expandable frame can expand to engage the valveseat of the docking station. The valve element can be connected to theexpandable frame. A pressure of blood acting on the valve and dockingstation can enhance retention by the retaining portions at the deployedposition.

The valve seat can be configured such that the valve seat is notsubstantially expanded radially outwardly by a radially outward force ofthe expandable valve. The range of sizes of the sealing portions can befrom 27 mm to 38 mm. The docking station can be configured to expandradially outwardly to varying degrees along its length L. Force appliedby the retaining portions can be in proportion to the pressure of bloodacting on the assembly. Force applied by the retaining portions can begreater when the heart is in a diastolic phase than when the heart is inthe systolic phase. The valve seat can be formed by a suture, ring,band, structural arrangement, material, foam, and in other ways. Thesealing portion can comprise a portion of a metal frame covered with afabric. The sealing portion can comprise an open cell foam or othermaterial. A portion of the docking station can be permeable to blood anda portion of the docking station can be impermeable to blood. A portionof the docking station that is impermeable to blood can extend from atleast the valve seat to at least the sealing portion. The dockingstation can be adjustable in length. The docking station can include afirst half (i.e., portion) that a second half (i.e., portion) of thedocking station can adjustably extend into to adjust the overall length.In other words, the length of the docking station can be adjusted bymoving the second half/portion relative to the first half/portion, andthe first half/portion may be moved independently from the secondhalf/portion (e.g., one half/portion may remain in place while the otherhalf/portion moves). If one of the first or second halves/portionsextends inside the other half/portion and overlaps to adjust the length,the first half/portion and second half/portion may be adjusted to changethe amount/length of overlap between the two. The one or more retainingportions can extend radially outward of the one or more sealing portionwhen the docking station is in an unconstrained state. Other featuresdescribed elsewhere in this disclosure may also be included.

In one exemplary embodiment, a method can include expanding a dockingstation and expanding a valve in the docking station. The dockingstation can be expanded such that a valve seat of the docking stationexpands to a valve seat deployed size and a sealing portion expands to asealing size that is within a range of sealing sizes. A frame of anexpandable valve can be expanded to engage the valve seat of the dockingstation. A pressure of blood acting on the valve and docking station canenhance retention by the retaining portions at the deployed position.The valve seat of the docking station can be configured such that adiameter of the valve seat is not increased more than 2 mm (or not morethan 1 mm, 3 mm, or 4 mm) by the radial outward force applied by theexpandable frame to the valve seat. The range of sealing sizes of thedocking station can be from 27 mm to 38 mm. The valve seat can be formedby a suture, ring, band, structural arrangement, material, foam, and inother ways. Other features/steps described elsewhere in this disclosuremay also be included.

In one embodiment, for example, a docking station can include a valveseat, and one or more sealing portions. The valve seat can be expandedto a deployed size. The one or more sealing portions can be connected tothe valve seat and extend radially outward of the valve seat. The one ormore sealing portions can be constructed to expand outward of the valveseat and provide a seal over a range of sizes. A length of the dockingstation can be adjustable. The docking station can include a first half(i.e., portion) that a second half (i.e., portion) of the dockingstation can adjustably extend into to adjust the overall length. Inother words, the length of the docking station can be adjusted by movingthe second half/portion relative to the first half/portion, and thefirst half/portion may be moved independently from the secondhalf/portion (e.g., one half/portion may remain in place while the otherhalf/portion moves). If one of the first or second halves/portionsextends inside the other half/portion and overlaps to adjust the length,the first half/portion and second half/portion may be adjusted to changethe amount/length of overlap between the two.

The valve seat can be constructed such that the valve seat is notsubstantially expandable radially outwardly by a radially outward forceof an expandable valve. A range of sizes of the sealing portion can befrom 27 mm to 38 mm. The docking station can be configured to expandradially outwardly to varying degrees along its length L. The valve seatand the one or more sealing portions can act as an isolator thatsubstantially prevents radial outward forces of an expandable valve frombeing transferred to the one or more sealing portions. The valve seatcan be formed by a suture, ring, band, structural arrangement, material,foam, and in other ways. The sealing portion can comprise a portion of ametal frame covered with a fabric. The sealing portion can comprises anopen cell foam. A portion of the docking station can be permeable toblood and a portion of the docking station can be impermeable to blood.Other features described elsewhere in this disclosure may also beincluded.

In one exemplary embodiment, a system can include an expandable dockingstation and an expandable valve. The expandable docking station caninclude a valve seat, and one or more sealing portions. The valve seatcan expand to a deployed size. The one or more sealing portions can beconnected to the valve seat and can extend radially outward of the valveseat. The one or more sealing portions can be constructed to expandoutward of the valve seat and provide a seal over a range of sizes. Alength of the docking station can be adjustable, e.g., adjustable in thesame or similar ways to those discussed elsewhere herein. The expandablevalve can comprise an expandable frame and a valve element. Theexpandable frame can expand to engage the valve seat of the dockingstation. The valve element can be connected to the expandable frame. Asecond half of the docking station may extend into a first half of thedocking station to make the length of the docking station adjustable.The valve seat may be configured such that the valve seat is notsubstantially expanded radially outwardly by a radially outward force ofthe expandable valve. The docking station can be configured to expandradially outwardly to varying degrees along its length L. The valve seatcan be formed by a suture, ring, band, structural arrangement, material,foam, and in other ways. The sealing portion can comprise a portion of ametal frame covered with a fabric. The sealing portion can comprise anopen cell foam. A portion of the docking station can be permeable toblood and a portion of the docking station can be impermeable to blood.Other features described elsewhere in this disclosure may also beincluded.

In one exemplary embodiment, a method can include expanding a multiplepiece docking station and expanding a valve in the docking station. Afirst docking station half or portion can be expanded. A portion/sectionof a second docking station half or portion can be positioned in thefirst docking station half, e.g., such that a desired length overlaps.The second docking station half can be expanded in the first dockingstation half to set a length of the docking station. The docking stationcan have valve seat and a sealing portion. A frame of an expandablevalve can be expanded to engage the valve seat of the docking station.The valve seat can be configured such that the valve seat is notsubstantially expanded radially outwardly by a radially outward force ofan expandable valve. A predetermined size of the sealing portion of thedocking station can be from 27 mm to 38 mm. The valve seat can be formedby a suture, ring, band, structural arrangement, material, foam, and inother ways. Other features/steps described elsewhere in this disclosuremay also be included.

In one exemplary embodiment, a delivery catheter can include and outertube and an inner tube. The outer tube can have a distal opening. Theinner tube can be disposed in the outer tube such that a gap is formedbetween the inner tube and the outer tube. The inner tube can have anopening at a proximal end and can have one or more side openings. Thedelivery catheter can be configured such that injecting flushing liquidinto the proximal end of the inner tube flushes the flushing liquidthrough the inner tube with at least some of the flushing liquid exitingthe inner tube through the one or more side openings to fill the gap andflush air out the distal opening of the outer tube. The inner tube canhave a distal opening and the delivery catheter can be configured suchthat the filling of the inner tube with the flushing liquid at theproximal end flushes the air out of the distal opening of the innertube. The inner tube can be filled with the flushing liquid at anopening for a guide wire at the proximal end of the inner tube. Thedelivery catheter can be configured such that the air in the inner tubecan be flushed out through the distal opening of the inner tube andthrough an opening in a nosecone that can be connected to the innertube. Other features described elsewhere in this disclosure may also beincluded.

In one exemplary embodiment, a method can flush air from a deliverycatheter. The delivery catheter can include an outer tube having adistal opening, an inner tube that has a proximal opening at a proximalend of the inner tube and one or more side openings, and a gap formed inbetween the inner tube and the outer tube. Flushing liquid can beinjected into the proximal end of the inner tube, such that the flushingliquid flows through the inner tube and at least some of the flushingliquid exits the inner tube through the one or more side openings tofill the gap and flush air out the distal opening of the outer tube. Theinner tube can be filled with the flushing liquid through the proximalopening, and the proximal opening can also be used for passing a guidewire through the delivery catheter. The delivery catheter can beinserted into a blood vessel after the air has been flushed out. Otherfeatures/steps described elsewhere in this disclosure may also beincluded.

In one exemplary embodiment, a catheter and docking station a sleeve, adocking station retainer, and a docking station. The docking stationretainer can be disposed in the sleeve. The docking station retainer caninclude one or more retainer recesses. The docking station can bedisposed in the sleeve. The docking station can include one or moreextensions releasably attached to the docking station retainer. Eachextension of the one or more extensions can include a head disposed inat least one of the one or more retainer recesses. Each extension of theone or more docking extensions can be configured to contact the dockingstation retainer at only two points. The head can be triangular and twoheads may be included. The one or more retainer recesses can be arectangular recess in the docking station retainer. Sides of the headcan extend away from one another at an angle of between 60 degrees and120 degrees. The sleeve can engage the one or more extensions to retainthe one or more heads in the retainer recess when the sleeve ispositioned over the one or more extensions. The one or more extensionscan spring radially outward relative to the docking station retainerwhen unconstrained by the sleeve to release the one or more extensionsfrom the docking station retainer. The one or more extensions can betilted in the one or more recesses. Other features described elsewherein this disclosure may also be included.

In one exemplary embodiment, a method of using a docking station caninclude placing a head of a docking station extension in a recess of adocking station retainer such that the docking station extensioncontacts the docking station retainer at only two points. The dockingstation and the docking station retainer can be placed in a sleeve. Thesleeve can engage the docking station extension to retain the head ofthe docking station extension in the recess. The head can be triangular.The recess can be a rectangular recess in the docking station retainer.Sides of the head can extend away from one another at an angle ofbetween 60 degrees and 120 degrees. The retainer and the docking stationcan be removed from the sleeve such that the head of the docking stationextension springs radially outward relative to the docking stationretainer to release the docking station extension from the dockingstation retainer. The extension can be tilted in the recess. Otherfeatures/steps described elsewhere in this disclosure may also beincluded.

In one exemplary embodiment, an assembly for deploying a docking stationincludes a handle and a catheter. The handle can include a housing, adrive member, and a driven member. The drive member can be rotatablycoupled to the housing. The driven member can be coupled to the drivemember and the housing, such that rotation of the drive member moves thedriven member linearly in the housing. The catheter can include andouter sleeve and an inner sleeve. The outer sleeve can be fixedlyconnected to the driven member. The inner sleeve can be disposed in theouter sleeve and can be fixedly connected to the housing. Rotation ofthe drive member can move the outer sleeve relative to the inner sleeve.The drive member can comprise a wheel having a gear portion. The drivemember can comprise an internally threaded member. The driven member cancomprise a gear rack. The driven member can comprise an externallythreaded member. A ratchet mechanism can be moveable from an engagedposition to a disengaged position, such that when the ratchet is in theengaged position the drive member is able to be rotated in only onedirection. A luer port may be fixed to the inner sleeve. A luer port andthe inner sleeve can be configured to accept a guide wire that extendsthrough the inner shaft. Other features described elsewhere in thisdisclosure may also be included.

In one exemplary embodiment, a method of deploying a docking station caninclude rotating a drive member relative to a housing to linearly move adriven member in the housing. An inner sleeve can be fixed to thehousing and an outer sleeve can be fixed to the driven member. Rotationof the drive member moves the outer sleeve relative to the inner sleeve.The drive member can linearly move the driven member by engagement ofgear teeth. The drive member can linearly move the driven member byengagement of threads. The drive member can be configured for rotationin only one direction. The first and second sleeves can be moved over aguide wire.

Various features as described elsewhere in this disclosure may beincluded in the examples summarized here and various methods and stepsfor using the examples and features may be used, including as describedelsewhere herein.

Further understanding of the nature and advantages of the disclosedinventions can be obtained from the following description and claims,particularly when considered in conjunction with the accompanyingdrawings in which like parts bear like reference numerals.

BRIEF DESCRIPTION OF THE DRAWINGS

To further clarify various aspects of embodiments of the presentdisclosure, a more particular description of the certain embodimentswill be made by reference to various aspects of the appended drawings.It is appreciated that these drawings depict only typical embodiments ofthe present disclosure and are therefore not to be considered limitingof the scope of the disclosure. Moreover, while the figures may be drawnto scale for some embodiments, the figures are not necessarily drawn toscale for all embodiments. Embodiments of the present disclosure will bedescribed and explained with additional specificity and detail throughthe use of the accompanying drawings.

FIG. 1A is a cutaway view of the human heart in a diastolic phase;

FIG. 1B is a cutaway view of the human heart in a systolic phase;

FIGS. 2A-2E are sectional views of pulmonary arteries illustrating thatpulmonary arteries may have a variety of different shapes and sizes;

FIGS. 3A-3D are perspective views of pulmonary arteries illustratingthat pulmonary arteries may have a variety of different shapes andsizes;

FIG. 4A is a schematic illustration of a compressed docking stationbeing positioned in a circulatory system;

FIG. 4B is a schematic illustration of the docking station of FIG. 4Aexpanded to set the position of the docking station in the circulatorysystem;

FIG. 4C is a schematic illustration of an expandable transcatheter heartvalve being positioned in the docking station illustrated by FIG. 4B;

FIG. 4D is a schematic illustration of the transcatheter heart valve ofFIG. 4C expanded to set the position of the heart valve in the dockingstation;

FIG. 4E illustrates the docking station and transcatheter heart valvedeployed in an irregularly shaped portion of the circulatory system;

FIG. 4F illustrates the docking station and transcatheter heart valvedeployed in a pulmonary artery;

FIG. 5A is a schematic illustration of a compressed docking stationbeing positioned in a circulatory system;

FIG. 5B is a schematic illustration of the docking station of FIG. 5Aexpanded to set the position of the docking station in the circulatorysystem;

FIG. 5C is a schematic illustration of an expandable transcatheter heartvalve being positioned in the docking station illustrated by FIG. 5B;

FIG. 5D is a schematic illustration of the transcatheter heart valve ofFIG. 5C expanded to set the position of the heart valve in the dockingstation;

FIG. 5E illustrates the docking station and transcatheter heart valvedeployed in an irregularly shaped portion of the circulatory system;

FIG. 5F illustrates the docking station and transcatheter heart valvedeployed in a pulmonary artery;

FIG. 6A is a cutaway view of the human heart in a systolic phase with adocking station and deployed in a pulmonary artery;

FIG. 6B is a cutaway view of the human heart in a systolic phase with adocking station and transcatheter heart valve deployed in a pulmonaryartery;

FIG. 7A is an enlarged schematic illustration of the docking station andtranscatheter heart valve of FIG. 6B when the heart is in the systolicphase;

FIG. 7B is a view taken in the direction indicated by lines 7B-7B inFIG. 7A;

FIG. 7C is a graph showing a relationship between a docking stationdiameter and a radial outward force applied by the docking station;

FIG. 8 is a cutaway view of the human heart in a diastolic phase with adocking station and transcatheter heart valve deployed in a pulmonaryartery;

FIG. 9A is an enlarged schematic illustration of the docking station andtranscatheter heart valve of FIG. 8 when the heart is in the diastolicphase;

FIG. 9B is a view taken in the direction indicated by lines 9B-9B inFIG. 9A;

FIG. 10A illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 10B illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 10C illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 10D illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 11A illustrates an exemplary embodiment of a telescoping dockingstation;

FIG. 11B illustrates an exemplary embodiment of a telescoping dockingstation;

FIG. 11C illustrates an exemplary embodiment of a telescoping dockingstation;

FIG. 11D illustrates an exemplary embodiment of telescoping dockingstation;

FIG. 12A illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 12B illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 12C illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 12D illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 13A illustrates an exemplary embodiment of a telescoping dockingstation;

FIG. 13B illustrates an exemplary embodiment of a telescoping dockingstation;

FIG. 13C illustrates an exemplary embodiment of a telescoping dockingstation;

FIG. 13D illustrates an exemplary embodiment of a telescoping dockingstation;

FIG. 14A illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 14B illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 14C illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 14D illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 14E illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 14F illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 14G illustrates an exemplary embodiment of a docking station with atranscatheter heart valve disposed inside the docking station;

FIG. 15A is a side view of an exemplary embodiment of a frame of adocking station;

FIG. 15B illustrates a side profile of the frame of illustrated by FIG.15A;

FIG. 16 illustrates the docking station frame of FIG. 15A in acompressed state;

FIG. 17A is a perspective view of the docking station frame of FIG. 15A;

FIG. 17B is a perspective view of the docking station frame of FIG. 15A;

FIG. 18 is a perspective view of an exemplary embodiment of a dockingstation having a plurality of covered cells and a plurality of opencells;

FIG. 19 is a perspective view of the docking station illustrated by FIG.18 with a portion cut away to illustrate a transcatheter heart valveexpanded into place in the docking station;

FIG. 20 illustrates a side profile of the docking station illustrated byFIG. 18 when implanted in a vessel of the circulatory system;

FIG. 21 illustrates a perspective view of the of the docking stationillustrated by FIG. 18 when installed in a vessel of the circulatorysystem;

FIG. 22 illustrates a perspective view of the of the docking station andvalve illustrated by FIG. 19 when implanted in a vessel of thecirculatory system;

FIGS. 23A and 23B illustrate a side profiles of the docking stationillustrated by FIG. 18 when implanted in different size vessels of thecirculatory system;

FIGS. 24 and 25 illustrate side profiles of the docking stationillustrated by FIG. 18 when implanted different sized vessels of thecirculatory system with a schematically illustrated transcatheter heartvalve having the same size installed or deployed in each dockingstation;

FIG. 26A is a sectional view illustrating a side profile of an exemplaryembodiment of a docking station placed in a pulmonary artery;

FIG. 26B is a sectional view illustrating a side profile of an exemplaryembodiment of a docking station placed in a pulmonary artery and aschematically illustrated valve placed in the docking station;

FIG. 26C is a sectional view illustrating an exemplary embodiment of adocking station placed in a pulmonary artery and a valve placed in thedocking station;

FIG. 27 is a side view of an exemplary embodiment of a docking station;

FIG. 28 is a side view of an exemplary embodiment of a telescopingdocking station;

FIG. 29 is a side view of the docking station of FIG. 28 where two partsof the docking station have been telescoped together;

FIG. 30 is a sectional view illustrating a docking station placed in apulmonary artery;

FIG. 31A is a sectional view illustrating a side profile of an exemplaryembodiment of a docking station placed in a pulmonary artery;

FIG. 31B is a sectional view illustrating a side profile of an exemplaryembodiment of a docking station placed in a pulmonary artery and a valveplaced in the docking station;

FIG. 32A is a cutaway view of the human heart in a systolic phase with adocking station and deployed in a pulmonary artery;

FIG. 32B is a cutaway view of the human heart in a systolic phase with adocking station and transcatheter heart valve deployed in a pulmonaryartery;

FIG. 33A is an enlarged schematic illustration of the docking stationand transcatheter heart valve of FIG. 32B when the heart is in thesystolic phase;

FIG. 33B is a view taken in the direction indicated by lines 33B-33B inFIG. 33A;

FIG. 34 is a cutaway view of the human heart, docking station, andtranscatheter heart valve deployed in the pulmonary artery illustratedby FIG. 32B when the heart is in the diastolic phase;

FIG. 35A is an enlarged schematic illustration of the docking stationand transcatheter heart valve of FIG. 34 when the heart is in thediastolic phase;

FIG. 35B is a view taken in the direction indicated by lines 35B-35B inFIG. 35A;

FIG. 36A is a cutaway view of the human heart in a systolic phase with adocking station being deployed in a pulmonary artery;

FIG. 36B is a cutaway view of the human heart in a systolic phase with adocking station deployed in a pulmonary artery;

FIG. 36C is a cutaway view of the human heart in a systolic phase with adocking station and transcatheter heart valve deployed in a pulmonaryartery;

FIG. 37A is an enlarged schematic illustration of the docking stationand transcatheter heart valve of FIG. 36C when the heart is in thesystolic phase;

FIG. 37B is a view taken in the direction indicated by lines 37B-37B inFIG. 37A;

FIG. 38 is a cutaway view of the human heart, docking station, andtranscatheter heart valve deployed in the pulmonary artery illustratedby FIG. 36C when the heart is in the diastolic phase;

FIG. 39A is an enlarged schematic illustration of the docking stationand transcatheter heart valve of FIG. 38 when the heart is in thediastolic phase;

FIG. 39B is a view taken in the direction indicated by lines 39B-39B inFIG. 39A;

FIG. 40A is a cutaway view of the human heart in a systolic phase with adocking station being deployed in a pulmonary artery;

FIG. 40B is a cutaway view of the human heart in a systolic phase with adocking station deployed in the pulmonary artery;

FIG. 40C is a cutaway view of the human heart in a systolic phase withthe docking station and a transcatheter heart valve deployed in thepulmonary artery;

FIG. 41A is an enlarged schematic illustration of the docking stationand transcatheter heart valve of FIG. 40C when the heart is in thesystolic phase;

FIG. 41B is a view taken in the direction indicated by lines 41B-41B inFIG. 41A;

FIG. 42 is a cutaway view of the human heart, docking station, andtranscatheter heart valve deployed in the pulmonary artery illustratedby FIG. 40C when the heart is in the diastolic phase;

FIG. 43A is an enlarged schematic illustration of the docking stationand transcatheter heart valve of FIG. 42 when the heart is in thediastolic phase;

FIG. 43B is a view taken in the direction indicated by lines 43B-43B inFIG. 43A;

FIGS. 44-47, and 48A-48C illustrate examples of valve types that may bedeployed in a docking station, e.g., one of the docking stationsdescribed or depicted herein;

FIG. 49A is a sectional view of an exemplary embodiment of a catheter;

FIG. 49B is a sectional view of an exemplary embodiment of a catheterwith a docking station crimped and loaded in the catheter;

FIGS. 50A-50D illustrate deployment of a docking station from acatheter;

FIG. 51 is a side view of an exemplary embodiment of a nosecone of acatheter;

FIG. 52 is a view taken as indicated by lines 52-52 in FIG. 51;

FIG. 53 is a sectional view of an exemplary embodiment of a distalportion of a catheter;

FIG. 54 is a side view of an exemplary embodiment of a nosecone of acatheter;

FIG. 55 is a sectional view of an exemplary embodiment of a distalportion of a catheter;

FIG. 56 is a perspective view of a holder for retaining a dockingstation in a catheter;

FIG. 57 is a perspective view of a holder for retaining a dockingstation in a catheter;

FIGS. 57A and 57B illustrate side views of extensions of a dockingstation disposed in the holder;

FIG. 58 is a sectional view of an exemplary embodiment of a handle for adocking station catheter;

FIG. 59 is an exploded perspective view of parts of the handle of FIG.58;

FIG. 60 is an exploded sectional view of parts of the handle of FIG. 58;

FIG. 61 is an exploded perspective sectional view of parts of the handleof FIG. 58;

FIG. 62 is a view of an exemplary embodiment of a handle for a dockingstation catheter with a side cover removed;

FIG. 63 is an enlarged portion of FIG. 62 illustrating a flushing systemof a catheter;

FIGS. 64A and 64B are views of the handle illustrated by FIG. 62 with anopposite side cover removed to illustrate extension and retraction of anouter sleeve of a docking station catheter;

FIG. 65 is an exploded view of the handle of FIG. 62;

FIG. 66 is a perspective view of the handle illustrated by FIG. 62 withthe opposite side cover removed

FIG. 67 is a side view of the handle illustrated by FIG. 62;

FIG. 68 is a side view of an indexing wheel of the handle illustrated byFIG. 62 in a ratcheting state;

FIG. 69 is a perspective view of the indexing wheel of FIG. 68 in theratcheting state;

FIG. 70 is an enlarged portion of FIG. 69;

FIG. 71 is a partial sectional view of the indexing wheel illustrated byFIG. 68 disposed in a handle housing;

FIG. 72 is a view that is similar to FIG. 71 in a disengaged state; and

FIG. 73 is a side view of an indexing wheel of the handle illustrated byFIG. 62 in the disengaged state.

DETAILED DESCRIPTION

The following description refers to the accompanying drawings, whichillustrate specific embodiments of the invention. Other embodimentshaving different structures and operation do not depart from the scopeof the present invention. Exemplary embodiments of the presentdisclosure are directed to devices and methods for providing a dockingstation or landing zone for a transcatheter heart valve (“THV”), e.g.,THV 29. In some exemplary embodiments, docking stations for THVs areillustrated as being used within the pulmonary artery, although thedocking stations (e.g., docking station 10) may be used in other areasof the anatomy, heart, or vasculature, such as the superior vena cava orthe inferior vena cava. The docking stations described herein can beconfigured to compensate for the deployed THV being smaller than thespace (e.g., anatomy/vasculature/etc.) in which it is to be placed.

It should be noted that various embodiments of docking stations andsystems for delivery and implant are disclosed herein, and anycombination of these options may be made unless specifically excluded.For example, any of the docking stations devices disclosed, may be usedwith any type of valve, and/or any delivery system, even if a specificcombination is not explicitly described. Likewise, the differentconstructions of docking stations and valves may be mixed and matched,such as by combining any docking station type/feature, valvetype/feature, tissue cover, etc., even if not explicitly disclosed. Inshort, individual components of the disclosed systems may be combinedunless mutually exclusive or otherwise physically impossible.

For the sake of uniformity, in these Figures and others in theapplication the docking stations are depicted such that the pulmonarybifurcation end is up, while the ventricular end is down. Thesedirections may also be referred to as “distal” as a synonym for up orthe pulmonary bifurcation end, and “proximal” as a synonym for down orthe ventricular end, which are terms relative to the physician'sperspective.

FIGS. 1A and 1B are cutaway views of the human heart H in diastolic andsystolic phases, respectively. The right ventricle RV and left ventricleLV are separated from the right atrium RA and left atrium LA,respectively, by the tricuspid valve TV and mitral valve MV; i.e., theatrioventricular valves. Additionally, the aortic valve AV separates theleft ventricle LV from the ascending aorta (not identified) and thepulmonary valve PV separates the right ventricle from the pulmonaryartery PA. Each of these valves has flexible leaflets extending inwardacross the respective orifices that come together or “coapt” in theflowstream to form the one-way, fluid-occluding surfaces. The dockingstations and valves of the present application are described primarilywith respect to the pulmonary valve. Therefore, anatomical structures ofthe right atrium RA and right ventricle RV will be explained in greaterdetail. It should be understood that the devices described herein mayalso be used in other areas, e.g., in the inferior vena cava and/or thesuperior vena cava as treatment for a regurgitant or otherwise defectivetri-cuspid valve, in the aorta (e.g., an enlarged aorta) as treatmentfor a defective aortic valve, in other areas of the heart orvasculature, in grafts, etc.

The right atrium RA receives deoxygenated blood from the venous systemthrough the superior vena cava SVC and the inferior vena cava IVC, theformer entering the right atrium from above, and the latter from below.The coronary sinus CS is a collection of veins joined together to form alarge vessel that collects deoxygenated blood from the heart muscle(myocardium), and delivers it to the right atrium RA. During thediastolic phase, or diastole, seen in FIG. 1A, the venous blood thatcollects in the right atrium RA enters the tricuspid valve TV byexpansion of the right ventricle RV. In the systolic phase, or systole,seen in FIG. 1B, the right ventricle RV contracts to force the venousblood through the pulmonary valve PV and pulmonary artery into thelungs. In one exemplary embodiment, the devices described by the presentapplication are used to replace or supplement the function of adefective pulmonary valve. During systole, the leaflets of the tricuspidvalve TV close to prevent the venous blood from regurgitating back intothe right atrium RA.

Referring to FIGS. 2A-2E and 3A-3D, the shown, non-exhaustive examplesillustrate that the pulmonary artery can have a wide variety ofdifferent shapes and sizes. For example, as shown in the sectional viewsof FIGS. 2A-2E and the perspective views of FIGS. 3A-3D, the length L,diameter, D, and curvature or contour may vary greatly between pulmonaryarteries of different patients. Further, the diameter D may varysignificantly along the length L of an individual pulmonary artery.These differences can be even more significant in pulmonary arteriesthat suffer from certain conditions and/or have been compromised byprevious surgery. For example, the treatment of Tetralogy of Fallot(TOF) or Transposition of the Great Arteries (TGA) often results inlarger and more irregularly shaped pulmonary arteries.

Tetralogy of Fallot (TOF) is a cardiac anomaly that refers to acombination of four related heart defects that commonly occur together.The four defects are ventricular septal defect (VSD), overriding aorta(the aortic valve is enlarged and appears to arise from both the leftand right ventricles instead of the left ventricle as in normal hearts),pulmonary stenosis (narrowing of the pulmonary valve and outflow tractor area below the valve that creates an obstruction of blood flow fromthe right ventricle to the pulmonary artery), and right ventricularhypertrophy (thickening of the muscular walls of the right ventricle,which occurs because the right ventricle is pumping at high pressure).

Transposition of the Great Arteries (TGA) refers to an anomaly where theaorta and the pulmonary artery are “transposed” from their normalposition so that the aorta arises from the right ventricle and thepulmonary artery from the left ventricle.

Surgical treatment for some conditions involves a longitudinal incisionalong the pulmonary artery, up to and along one of the pulmonarybranches. This incision can eliminate or significantly impair thefunction of the pulmonary valve. A trans-annular patch is used to coverthe incision after the surgery. The trans-annular patch reduces stenoticor constrained conditions of the pulmonary artery PA, associated withother surgeries. However, the impairment or elimination of the pulmonaryvalve PV can create significant regurgitation and, prior to the presentinvention, often required later open heart surgery to replace thepulmonary valve. The trans-annular patch technique can result inpulmonary arteries having a wide degree of variation in size and shape(See FIGS. 3A-3D)

Referring to FIGS. 4A-4F, in one exemplary embodiment an expandabledocking station 10 includes one or more sealing portions 410, a valveseat 18, and one or more retaining portions 414. The sealing portion(s)410 provide a seal between the docking station 10 and an interiorsurface 416 of the circulatory system. The valve seat 18 provides asupporting surface for implanting or deploying a valve 29 in the dockingstation 10 after the docking station 10 is implanted in the circulatorysystem. The retaining portions 414 help retain the docking station 10and the valve 29 at the implantation position or deployment site in thecirculatory system. Expandable docking station 10 and valve 29 asdescribed in the various embodiments herein are also representative of avariety of docking stations and/or valves that might be known ordeveloped, e.g., a variety of different types of valves could besubstituted for and/or used as valve 29 in the various docking stations.

FIGS. 4A-4D schematically illustrate an exemplary deployment of thedocking station 10 and valve 29 in the circulatory system. Referring toFIG. 4A, the docking station 10 is in a compressed form/configurationand is introduced to a deployment site in the circulatory system. Forexample, the docking station 10, may be positioned at a deployment sitein a pulmonary artery by a catheter (e.g., catheter 3600 as shown inFIGS. 50A-50D). Referring to FIG. 4B, the docking station 10 is expandedin the circulatory system such that the sealing portion(s) 410 and theretaining portions 414 engage the inside surface 416 of a portion of thecirculatory system. Referring to FIG. 4C, after the docking station 10is deployed, the valve 29 is in a compressed form and is introduced intothe valve seat 18 of the docking station 10. Referring to FIG. 4D, thevalve 29 is expanded in the docking station, such that the valve 29engages the valve seat 18. In the examples depicted herein, the dockingstation 10 is longer than the valve. However, in other embodiments thedocking station 10 can be the same length or shorter than the length ofthe valve 29. Similarly, the valve seat 18 can be longer, shorter, orthe same length as the length of the valve 29.

Referring to FIG. 4D, the valve 29 has expanded such that the seat 18 ofthe docking station supports the valve. The valve 29 only needs toexpand against the narrow seat 18, rather than against the wider spacewithin the portion of the circulatory system that the docking station 10occupies. The docking station 10 allows the valve 29 to operate withinthe expansion diameter range for which it is designed.

FIG. 4E illustrates that the inner surface 416 of the circulatorysystem, such as the inner surface of a blood vessel or anatomy of theheart can vary in cross-section size and/or shape along its length. Inan exemplary embodiment, the docking station 10 is configured to expandradially outwardly to varying degrees along its length L to conform toshape of the inner surface 416. In one exemplary embodiment, the dockingstation 10 is configured such that the sealing portion(s) 410 and/or theretaining portion(s) engage the inner surface 416, even though the shapeof the blood vessel or anatomy of the heart vary significantly along thelength L of the docking station. The docking station can be made from avery resilient or compliant material to accommodate large variations inthe anatomy. For example, the docking station can be made from a highlyflexible metal, metal alloy, polymer, or an open cell foam. Examples ofa metals and metal alloys that can be used include, but are not limitedto, nitinol, elgiloy, and stainless steel, but other metals and highlyresilient or compliant non-metal materials can be used. For example, thedocking station 10 can have a frame or portion of a frame (e.g., aself-expanding frame, retaining portion(s), sealing portion(s), valveseat, etc.) made of these materials, e.g., from shape memory materials,such as nitinol. These materials allow the frame to be compressed to asmall size, and then when the compression force is released, the framewill self-expand back to its pre-compressed diameter.

An example of an open cell foam that can be used to form the dockingstation or a portion of the docking station is a bio-compatible foam,such as a polyurethane foam (e.g., as may be obtained from Biomerix,Rockville, Md.). Docking stations described herein can be self-expandingand/or expandable with an inflatable device to cause the docking stationto engage an inner surface 416 having a variable shape.

FIG. 4F illustrates the docking station 10 and a valve 29 implanted in apulmonary artery PA. As mentioned with respect to FIGS. 2A-2E and 3A-3D,the shape of the pulmonary artery may vary significantly along itslength. In one exemplary embodiment, the docking station 10 isconfigured to conform to the varying shape of the pulmonary artery PA inthe same manner as described with respect to FIG. 4E.

Referring to FIGS. 5A-5F, in one exemplary embodiment an expandabledocking station 10 is made from an expandable foam material, such as anopen cell biocompatible foam. The outer surface 510 of the foam materialcan serve as the sealing portion 410. In this example, a valve seat 18can be provided on the inner surface 512 of the foam material asillustrated, or the inner surface 512 can serve as the valve seat. Inthe example illustrated by FIGS. 5A-5F, the retaining portions 414 areomitted, though retaining portions can be used. In one embodiment, foammaterial can be used together with an expandable frame (e.g., of metal,shape memory material, etc.). The foam material can cover or extend thefull length of the frame or only a portion of the length of the frame.

FIGS. 5A-5D schematically illustrate deployment of the foam dockingstation 10 and valve 29 in the circulatory system. Referring to FIG. 5A,the docking station 10 is in a compressed form and is introduced to adeployment site in the circulatory system. For example, the dockingstation 10, may be positioned at a deployment site in a pulmonary arteryby a catheter (e.g., catheter 3600 shown in FIGS. 50A-50D). Referring toFIG. 5B, the docking station 10 is expanded in the circulatory systemsuch that the sealing portion 410 engage the inside surface 416 of thecirculatory system. Referring to FIG. 5C, after the docking station 10is deployed, the valve 29 is in a compressed form and is introduced intothe valve seat 18 or inner surface 512 of the docking station 10.Referring to FIG. 5D, the valve 29 is expanded in the docking station,such that the valve 29 engages the valve seat 18 or inner surface 512(e.g., where inner surface 512 acts as the valve seat).

FIG. 5E illustrates that the inner surface 416 of the circulatorysystem, such as the inner surface of a blood vessel or anatomy of theheart may vary in cross-section along its length. In an exemplaryembodiment, the foam docking station 10 is configured to expand radiallyoutwardly to varying degrees along its length L to conform to shape ofthe inner surface 416.

FIG. 5F illustrates the foam docking station 10 and a valve 29 implantedin a pulmonary artery PA. As mentioned with respect to FIGS. 2A-2E and3A-3D, the shape of the pulmonary artery may vary significantly alongits length. In one exemplary embodiment, the docking station 10 isconfigured to conform to the varying shape of the pulmonary artery PA inthe same or a similar manner as described with respect to FIG. 4E.

Referring to FIG. 6A, a docking station, e.g., a docking station asdescribed with respect to FIGS. 4A-4D, is deployed in the pulmonaryartery PA of a heart H. FIG. 6B illustrates a valve 29 deployed in thedocking station 10 illustrated by FIG. 6A. In FIGS. 6A and 6B, the heartis in the systolic phase. FIG. 7A is an enlarged representation of thedocking station 10 and valve 29 in the pulmonary artery 29 of FIG. 6B.When the heart is in the systolic phase, the valve 29 opens. Blood flowsfrom the right ventricle RV and through the pulmonary artery PA, dockingstation 10, and valve 29 as indicated by arrows 602. FIG. 7B illustratesspace 608 that represents the valve 29 being open when the heart is inthe systolic phase. FIG. 7B does not show the interface between thedocking station 10 and the pulmonary artery to simplify the drawing. Thecross-hatching in FIG. 7B illustrates blood flow through the open valve.In an exemplary embodiment, blood is prevented from flowing between thepulmonary artery PA and the docking station 10 by the sealing portion(s)410 and blood is prevented from flowing between the docking station 10and the valve 29 by seating of the valve 29 in the seat 18 of thedocking station 10. In this example, blood is substantially only flowingor only able to flow through the valve 29 when the heart is in thesystolic phase.

FIG. 8 illustrates the valve 29, docking station 10 and heart Hillustrated by FIG. 6B, when the heart is in the diastolic phase.Referring to FIGS. 9A and 9B, when the heart is in the diastolic phase,the valve 29 closes. FIG. 9A is an enlarged representation of thedocking station 10 and valve 29 in the pulmonary artery 29 of FIG. 8.Blood flow in the pulmonary artery PA above the valve 29 (i.e. in thepulmonary branch 760) is blocked by the valve 29 being closed andblocking blood flow as indicated by arrow 900. The solid area 912 inFIG. 9B represents the valve 29 being closed when the heart is in thediastolic phase.

In one exemplary embodiment, the docking station 10 acts as an isolatorthat prevents or substantially prevents radial outward forces of thevalve 29 from being transferred to the inner surface 416 of thecirculatory system. In one embodiment, the docking station 10 includes avalve seat 18 (which is not expanded radially outwardly or is notsubstantially expanded radially outward by the radially outward force ofthe THV or valve 29, i.e., the diameter of the valve seat is notincreased or is increased by less than 4 mm by the force of the THV),and anchoring/retaining portions 414 and sealing portions 410, whichimpart only relatively small radially outward forces 720, 722 on theinner surface 416 of the circulatory system (as compared to the radiallyoutward force applied to the valve seat 18 by the valve 29).

When no docking station is used, stents and frames of THVs are held inplace in the circulatory system by a relatively high radial outwardforce 710 of the stent or frame 712 of the THV acting directly on theinside surface 416 of the circulatory system. If a docking station isused, as in the example illustrated by FIG. 7A, the stent or frame 712of the valve 29 expands radially outward or is expanded radially outwardto impart the high force 710 on the valve seat 18 of the docking station10. This high radially outward force 710 secures the valve 29 to thevalve seat 18 of the docking station 10. However, since the valve seat18 is not expanded or is not substantially expanded by the force 710,the force 710 is isolated from the circulatory system, rather than beingused to secure the docking station in the circulatory system.

In an exemplary embodiment, the radially outward force 722 of thesealing portions 410 to the inside surface 416 is substantially smallerthan the radially outward force 710 applied by the valve 29 to the valveseat 18. For example, the radially outward sealing force 722 can be lessthan ½ the radially outward force 710 applied by the valve, less than ⅓the radially outward force 710 applied by the valve, less than ¼ theradially outward force 710 applied by the valve, less than ⅛, or evenless than 1/10 the radially outward force 710 applied by the valve. Inone exemplary embodiment, the radially outward force 722 of the sealingportions 410 is selected to provide a seal between the inner surface 416and the sealing portion 410, but is not sufficient by itself to retainthe position of the valve 29 and docking station 10 in the circulatorysystem.

In an exemplary embodiment, the radially outward force 720 of theanchoring/retaining portions 414 to the inside surface 416 issubstantially smaller than the radially outward force 710 applied by thevalve 29 to the valve seat 18. For example, the radially outward sealingforce 720 can be less than ½ the radially outward force 710 applied bythe valve, less than ⅓ the radially outward force 710 applied by thevalve, less than ¼ the radially outward force 710 applied by the valve,less than ⅛, or even less than 1/10 the radially outward force 710applied by the valve.

In one exemplary embodiment, the radially outward force 720 of theretaining portions 414 is not sufficient by itself to retain theposition of the valve 29 and docking station 10 in the circulatorysystem. Rather, the pressure of the blood 608 is used to enhance theretention of the retaining portions 414 to the inside surface 416.Referring again to FIG. 6A, when the heart is in the systolic phase, thevalve 29 is open and blood flows through the valve as indicated byarrows 602. Since the valve 29 is open and blood flows through the valve29, the pressure P applied to the docking station 10 and valve 29 by theblood is low as indicated by the small P and arrow in FIG. 7A. Eventhough small, the pressure P forces the docking station and its upperretaining portions 414 against the surface 416 generally in thedirection indicated by arrow F. This blood flow assisted force F appliedby the retaining portions F to the surface 416 prevents the dockingstation 10 and valve 29 from moving in the direction 602 of blood flowin the systolic phase of the heart H.

Referring to FIG. 9A, when the heart is in the diastolic phase, thevalve 29 is closed and blood flow is blocked as indicated by arrow 900.Since the valve 29 is closed and the valve 29 and docking station 10block the flow of blood, the pressure P applied to the docking station10 and valve 29 by the blood is high as indicated by the large arrow Pin FIG. 9A. This large pressure P forces the lower retaining portions414 against the surface 416 generally in the direction indicated by thelarge arrows F. This blood flow assisted force F applied by theretaining portions F to the surface 416 prevents the docking station 10and valve 29 from moving in the direction indicated by arrow 900.

Since the force applied by the upper and lower retaining portions 414 isdetermined by amount of pressure applied to the valve 29 and dockingstation 10 by the blood, the force applied to the surface 416 isautomatically proportioned. That is, the upper retaining portions areless forcefully pressed against the surface 416 when the heart is in thesystolic phase than the lower retaining portions are pressed against thesurface 416 when the heart is in the diastolic phase. This is becausethe pressure against the open valve 29 and docking station 10 in thesystolic phase is less than the pressure against the closed valve anddocking station in the diastolic phase.

The valve seat 18 and sealing portion 410 can take a wide variety ofdifferent forms. For example, the valve seat 18 can be any structurethat is not expanded radially outwardly or is not substantially expandedradially outward by the radially outward force of the THV (i.e., thediameter of the valve seat in the deployed position/configuration maynot expand or may expand less than 4 mm, e.g., the diameter may onlyexpand 1-4 mm larger when the valve is deployed in the valve seat). Forexample, the valve seat 18 can comprise a suture or a metal ring thatresists or limits expansion. However, in one embodiment, the valve seat18 (or any valve seat described herein) can be expandable over a largerrange, for example, the diameter may expand between 5 mm and 30 mmlarger when a valve is deployed in the valve seat. In one embodiment,the diameter might expand from 5 mm or 6 mm in diameter to 20 mm-29 mm,24 mm, 26 mm, 29 mm, etc. in diameter, or expand from and to differentdiameters within that range. Even if more expandable, the valve seat canstill be restricted in expansion, e.g., restricted to avoid expansion ofthe valve seat beyond an expanded diameter of a valve to be placed inthe valve seat or to avoid expansion beyond a diameter that willsecurely hold the valve in the valve seat via the forces createdtherebetween. The valve seat 18 can be part of or define a portion ofthe body of the docking station 10, or the valve seat 18 can be aseparate component that is attached to the body of the docking station.The valve seat 18 can be longer, shorter, or the same length as thevalve. The valve seat 18 can be significantly shorter than the valve 29when the valve seat 18 is defined by a suture or a metal ring. A valveseat 18 formed by a suture or metal ring can form a narrowcircumferential seal line between the valve 29 and the docking station.

The sealing portion(s) 410 of various embodiments can take a widevariety of different forms. For example, the sealing portion(s) 410 canbe any structure that provides a seal(s) between the docking station 10and the surface 416 of the circulatory system. For example, the sealingportion(s) 410 can comprise a fabric, a foam, biocompatible tissue, acombination of these, etc. The sealing portion(s) 410 can be part of ordefine a portion of the body of the docking station 10, and/or thesealing portion(s) 410 can be a separate component that is attached tothe body of the docking station. The docking station 10 may include asingle sealing portion 410 or two, or more than two sealing portions.

As mentioned above, in one exemplary embodiment the sealing portion(s)410 is configured to apply a low radially outward force to the surface416. The low radially outward force can be provided in a wide variety ofdifferent ways. For example, sealing portion may be made from a verycompressible or compliant material. Referring to FIG. 7C, in oneexemplary embodiment, the docking station 10 body is made from anelastic or superelastic metal. One such metal is nitinol. When the bodyof a docking station 10 is made from a lattice of metal struts, the bodycan have the characteristics of a spring. Referring to FIG. 7C, like aspring, when the body of the docking station is unconstrained andallowed to relax to its largest diameter the body of the docking stationapplies little or no radially outward force. As the body of the dockingstation 10 is compressed, like a spring, the radially outward forceapplied by the docking station increases. As is illustrated by FIG. 7C,in one exemplary embodiment the relationship of the radially outwardforce of the docking station body to the expanded diameter of thedocking station is non-linear, although, in one exemplary embodiment,the relationship could also be linear. In the example illustrated byFIG. 7C, the curve 750 illustrates the relationship between the radiallyoutward force exerted by the docking station 10 and the compresseddiameter of the docking station. In the region 752, the curve 750 has alow slope. In this region 752 the radially outward force is low andchanges only a small amount. In one exemplary embodiment, the region 752corresponds to a diameter between 25 mm and 40 mm, such as between 27 mmand 38 mm. The radially outward force is small in the region 752, but isnot zero. In the region 754, the curve 750 has a higher slope. In thisregion 754 the radially outward force increases significantly as thedocking station is compressed. In one exemplary embodiment, the body ofthe stent is constructed to be in the low slope region 752. This allowsthe sealing portions 710 to apply only a small radially outward force tothe inner surface 416 of the circulatory system over a wide range ofdiameters.

The retaining portions 414 can take a wide variety of different forms.For example, the retaining portion(s) 414 may be any structure that setsthe position of the docking station 10 in the circulatory system. Forexample, the retaining portion(s) 414 may press against or into theinside surface 416 or extend around anatomical structure of thecirculatory system to set the position of the docking station 10. Theretaining portion(s) 414 may be part of or define a portion of the bodyof the docking station 10 or the retaining portion(s) 414 may be aseparate component that is attached to the body of the docking station.The docking station 10 may include a single retaining portion 414 ortwo, or more than two retaining portions.

FIGS. 10A-10C illustrate that the docking station 10 can have anycombination of one or more than one different types of valve seats 18and sealing portions 410. In the example illustrated by FIG. 10A, thevalve seat 18 is a separate component that is attached to the body ofthe docking station 10 and the sealing portion is integrally formed withthe body of the docking station. In the example illustrated by FIG. 10B,the valve seat 18 is a separate component that is attached to the bodyof the docking station 10 and the sealing portion 410 is a separatecomponent that is attached to the body of the docking station. In theexample illustrated by FIG. 10C, the valve seat 18 is integrally formedwith the body of the docking station 10 and the sealing portion isintegrally formed with the body of the docking station. In the exampleillustrated by FIG. 10D, the valve seat 18 is integrally formed with thebody of the docking station 10 and the sealing portion is a separatecomponent that is attached to the body of the docking station 10.

As mentioned above, the length of the pulmonary artery PA and otheranatomical structures of the circulatory system may vary greatly frompatient to patient. Referring to FIGS. 11A-11D, in one exemplaryembodiment the length of the docking station 10 is adjustable asindicated by arrow 1100. This adjustability 1100 refers to the abilityof the implanted/expanded length of the docking station to be adjusted,rather than the inherent change in length that occurs when a stentexpands from a compressed state to an expanded state. The length may beadjusted in a wide variety of different ways. In the example illustratedby FIGS. 11A-11D, the docking station 10 includes a first half 1102 anda second half 1104. The use of the word “half” as used herein withrespect to two part docking stations is synonymous with “portion” anddoes not require the first and second half or first and second portionto be equal in size, i.e., the first half could be larger/longer thanthe second half and vice versa. In one embodiment, the second half 1104can be inserted or “telescoped” into the first half 1102. The amount ofinsertion or “telescoping” sets the length of the docking station 10.Any of the docking stations 10 shown and described in this patentapplication can be adjustable in length by making the docking stationsfrom two parts that are telescoped together or are otherwise adjustablerelative to each other. In one embodiment, a length of a single-piecedocking station can be collapsible and expandable. In one embodiment, adocking station may be formed of a material that can change shape toadjust the length. In one embodiment, more than two portions (e.g., 3,4, or more portions) can be combined in similar ways and include one ormore similar features as first half 1102 and second half 1104.

In one exemplary embodiment, the length of the docking station 10 can beadjusted in the pulmonary artery PA by first deploying the first half1102 of the docking station 10 in the pulmonary artery. For example, thefirst half 1102 may be positioned and expanded as desired, e.g., suchthat a distal end 1106 of the first half is aligned with or extendssomewhat past the branch of the pulmonary artery. After the first half1102 is expanded in the pulmonary artery, the compressed second half1104 can be positioned with a distal end 1110 disposed in the proximalend 1108 of the first half 1102. In one embodiment, the position of thesecond half 1104 is selected such that the sealing portion 410 andretaining portion 414 will make contact with the pulmonary artery andset the position of the docking station 10 in the pulmonary artery. Onceproperly positioned, the second half 1104 is expanded. In oneembodiment, the distal end of 1110 of the second half 1104 frictionallyengages the proximal end 1108 of the first half to secure the two halves1102, 1104 together. In one embodiment, a lock(s), locking mechanism,suture(s), interlacing, link(s) and/or other attachment device/mechanismmay be used to help secure the halves/portions together.

In the examples illustrated by FIGS. 11A-11D, the seat 18 and thesealing portion 410 are included on the second half 1104 of the dockingstation 10. However, in other embodiments the seat 18 and/or the sealingportion 410 can be included on the first half 1102. FIGS. 11A-11Cillustrate that the halves 1102, 1104 of the docking station 10 can haveany combination of different types of valve seats 18 and sealingportions 410. In the example illustrated by FIG. 11A, the valve seat 18is a separate component that is attached to the body of the dockingstation half 1104 and the sealing portion is integrally formed with thebody of the docking station half 1104. In the example illustrated byFIG. 11B, the valve seat 18 is a separate component that is attached tothe body of the docking station half 1104 and the sealing portion 410 isa separate component that is attached to the body of the docking stationhalf 1104. In the example illustrated by FIG. 11C, the valve seat 18 isintegrally formed with the body of the docking station half 1104 and thesealing portion is integrally formed with the body of the dockingstation half 1104. In the example illustrated by FIG. 11D, the valveseat 18 is integrally formed with the body of the docking station half1104 and the sealing portion 410 is a separate component that isattached to the body of the docking station half 1104.

FIGS. 12A-12D illustrate exemplary embodiments of docking stations 10with two sealing portions 410. The docking station 10 can have anycombination of one or more than one different types of valve seats 18and sealing portions 410. In the example illustrated by FIG. 12A, thevalve seat 18 is a separate component that is attached to the body ofthe docking station 10 and the sealing portions 410 is integrally formedwith the body of the docking station. In the example illustrated by FIG.12B, the valve seat 18 is a separate component that is attached to thebody of the docking station 10 and the sealing portions 410 are separatecomponents that are attached to the body of the docking station. In theexample illustrated by FIG. 12C, the valve seat 18 is integrally formedwith the body of the docking station 10 and the sealing portions areintegrally formed with the body of the docking station. In the exampleillustrated by FIG. 12D, the valve seat 18 is integrally formed with thebody of the docking station 10 and the sealing portions are separatecomponents that are attached to the body of the docking station 10.

FIGS. 13A-13D illustrate that the docking stations illustrated by FIGS.12A-12D can be two-piece telescoping docking stations. The pieces 1102,1104 of the docking station 10 can have any combination of one or morethan one different types of valve seats 18 and sealing portions 410 oneither or both of the two pieces. In the example illustrated by FIG.13A, the first half 1102 includes an integral sealing portion 410. Thesecond half 1104 includes a valve seat 18 that is a separate componentthat is attached to the body of the docking station 10 and the sealingportions 410 is integrally formed with the body of the docking station.In the example illustrated by FIG. 13B, the first half 1102 includes asealing portion 410 that is separate from the body of the first half102. The valve seat 18 is a separate component that is attached to thebody of the docking station 10 and the sealing portion 410 is a separatecomponents that is attached to the body of the docking station. In theexample illustrated by FIG. 13C, the first half 1102 includes anintegral sealing portion 410. The valve seat 18 is integrally formedwith the body of the second half 1104 of the docking station 10 and thesealing portion 410 is integrally formed with the body of the secondhalf 1104. In the example illustrated by FIG. 12D, the first half 1102includes a sealing portion 410 that is separate from the body of thefirst half 102. The valve seat 18 is integrally formed with the body ofthe second half 1104 of the docking station 10 and the sealing portion410 is a separate components that is attached to the body of the secondhalf 1104.

Referring to FIGS. 14A-14G, in one exemplary embodiment the dockingstation 10 can include a permeable portion 1400 that blood can flowthrough as indicated by arrows 1402 and an impermeable portion 1404 thatblood cannot flow through. In one exemplary embodiment, the impermeableportion 1404 extends from at least the sealing portion 410 to the valveseat 18 to prevent blood from flowing around the valve 29. In oneexemplary embodiment, the permeable portion 1400 allows blood to freelyflow through it, so that portions of the docking station that do notseal against the inside surface 416 of the circulatory system or sealagainst the valve 29 do not block the flow of blood. For example, thedocking station 10 may extend into the branch of the pulmonary arteryand the portion 1400 of the docking station 10 that extends into thepulmonary artery freely allows blood to flow through the docking station10. In one exemplary embodiment, the permeable portion 1400 allows bloodto freely flow through it, so that areas 1420 between the dockingstation and the circulatory system are flushed with blood as the heartbeats, thereby preventing blood stasis in the areas 1420.

The impermeable portion 1404 can take a wide variety of different forms.The impermeable portion 1404 may be any structure or material thatprevents blood to flow through the impermeable portion 1404. Forexample, the body of the docking station 10 can be formed from wires ora lattice, such as a nitinol wire or lattice, and cells of body arecovered by an impermeable material (See FIG. 18). A wide variety ofdifferent materials may be used as the impermeable material. Forexample, the impermeable material may be a blood-impermeable cloth, suchas a PET cloth or biocompatible covering material such as a fabric thatis treated with a coating that is impermeable to blood, polyester, or aprocessed biological material, such as pericardium.

FIGS. 14A-14G illustrate that a wide variety of docking stationconfigurations can be provided with a permeable portion 1402. Thesealing portion 410 may be integrally formed with the body of thedocking station as illustrated by FIGS. 14B, 14D, and 14F or separate asillustrated by FIGS. 14C, 14E and 14G. In FIGS. 14F and 14G the dockingstation 10 includes portions 1410. These portions 1410 are similar tothe sealing portions 410, but a seal is not formed with the innersurface 416 of the circulatory system, because the portion 1410 is partof the permeable portion 1402. The valve seat 18 may be separatelyformed from the body of the docking station as illustrated by FIGS.14A-14C or integrally formed with the body of the docking station 10 asillustrated by FIGS. 14D-14G.

FIGS. 15A, 15B, 16, 17A, and 17B illustrate an exemplary embodiment of aframe 1500 or body of a docking station 10. The frame 1500 or body cantake a wide variety of different forms and FIGS. 15A, 15B, 16, 17A, and17B illustrate just one of the many possible configurations. In theexample illustrated by FIGS. 15A, 15B, 16, 17A, 17B, and 18, the dockingstation 10 has a relatively wider proximal inflow end 12 and distaloutflow end 14, and a relatively narrower portion 16 that forms the seat18 in between the ends 12, 14. In the example illustrated by FIGS. 15A,15B, 17A, and 17B, the frame 1500 of the docking station 10 ispreferably a wide stent comprised of a plurality of metal struts 1502that form cells 1504. In the example of FIGS. 15A, 15B, 17A, and 17B,the frame 1500 has a generally hourglass-shape that has a narrow portion16, which forms the valve seat 18 when covered by an impermeablematerial, in between the proximal and distal ends 12, 14. As describedbelow, the valve 18 expands in the narrow portion 16, which forms thevalve seat 18.

FIGS. 15A, 15B, 17A, and 17B illustrate the frame 1500 in itsunconstrained, expanded condition. In this exemplary embodiment, theretaining portions 414 comprise ends 1510 of the metal struts 1502 atthe proximal and distal ends 12, 14. The sealing portion 410 is betweenthe retaining portions 414 and the waist 16. In the unconstrainedcondition, the retaining portions 414 extend generally radially outwardand are radially outward of the sealing portion 410. FIG. 16 illustratesthe frame 16 in the compressed state for delivery and expansion by acatheter. The docking station can be made from a very resilient orcompliant material to accommodate large variations in the anatomy. Forexample, the docking station can be made from a highly flexible metal,metal alloy, polymer, or an open cell foam. An example of a highlyresilient metal is nitinol, but other metals and highly resilient orcompliant non-metal materials can be used. The docking station 10 may beself-expanding, manually expandable (e.g., expandable via balloon), ormechanically expandable. A self-expanding docking station 10 may be madeof a shape memory material such as, for example, nitinol.

FIG. 18 illustrates the frame 1500 with impermeable material 21 attachedto the frame 1500 to form the docking station 10. Referring to FIG. 18,in one exemplary embodiment a band 20 extends about the waist or narrowportion 16, or is integral to the waist to form an unexpandable orsubstantially unexpandable valve seat 18. The band 20 stiffens the waistand, once the docking station is deployed and expanded, makes thewaist/valve seat relatively unexpandable in its deployed configuration.In the example illustrated by FIG. 19, the valve 29 is secured byexpansion of its collapsible frame into the narrow portion 16, whichforms the valve seat 18, of the docking station 10. As is explainedabove, the unexpandable or substantially unexpandable valve seat 18prevents the radially outward force of the valve 29 from beingtransferred to the inside surface 416 of the circulatory system. Howeverin another exemplary embodiment, the waist/valve seat of the deployeddocking station may optionally expand slightly in an elastic fashionwhen the valve is deployed against it. This optional elastic expansionof the waist 18 may put pressure on the valve 29 to help hold the valve29 in place within the docking station.

The band can take a wide variety of different forms and can be made froma wide variety of different materials. The band 20 can be made of PET,one or more sutures, fabric, metal, polymer, a biocompatible tape, orother relatively unexpandable materials known in the art that aresufficient to maintain the shape of the valve seat 18 and hold the valve29 in place. The band can extend about the exterior of the stent, or canbe an integral part of it, such as when fabric or another material isinterwoven into or through cells of the stent. The band 20 may benarrow, such as the suture band in FIG. 18, or may be wider. The bandcan be a variety of widths, lengths, and thicknesses. In onenon-limiting example, the valve seat 18 is between 27-28 mm wide,although the diameter of the valve seat should be within the operatingrange of the particular valve 29 that will be secured within the valveseat 18, and can be different than the foregoing example. The valve 29,when docked within the docking station, can optionally expand aroundeither side of the valve seat slightly. This aspect, sometimes referredto as a “dogbone” (e.g., because of the shape it forms around the valveseat or band), can also help hold the valve in place.

FIGS. 20 and 21 illustrate the docking station 10 of FIG. 18 implantedin the circulatory system, such as in the pulmonary artery. The sealingportions 410 provide a seal between the docking station 10 and aninterior surface 416 of the circulatory system. In the example of FIGS.20 and 21, the sealing portion 410 is formed by providing an impermeablematerial 21 (See FIG. 21) over the frame 1500 or a portion thereof, Inparticular, the sealing portion 410 can comprise the lower, rounded,radially outward extending portion 2000 of the frame 1500. In anexemplary embodiment, the impermeable material 21 extends from at leastthe portion 2000 of the frame 1500 to the valve seat 18. This makes thedocking station impermeable from the sealing portion 410 to the valveseal 18. As such, all blood flowing in the inflow direction 12 towardthe outflow direction 14 is directed to the valve seat 18 (and valve 29once installed or deployed in the valve seat).

In a preferred embodiment of a docking station 10, the inflow portionhas walls that are impermeable to blood, but the outflow portion wallsare relatively open. In one approach, the inflow end portion 12, themid-section 16, and a portion of the outflow end portion 14 are coveredwith a blood-impermeable fabric 21, which may be sewn onto the stent orotherwise attached by a method known in the art. The impermeability ofthe inflow portion of the stent helps to funnel blood into the dockingstation 10 and ultimately flow through the valve that is to be expandedand secured within the docking station 10.

From another perspective, this embodiment of a docking station isdesigned to seal at the proximal inflow section 2000 to create a conduitfor blood flow. The distal outflow section, however, is generally leftopen, thereby allowing the docking station 10 to be placed higher in thepulmonary artery without restricting blood flow. For example, thepermeable portion 1400 may extend into the branch of the pulmonaryartery and not impede or not significantly impede the flow of blood pastthe branch. In one embodiment, blood-impermeable cloth, such as a PETcloth for example, or other material covers the proximal inflow section,but the covering does not cover any or at least a portion of the distaloutflow section 14. As one non-limiting example, when the dockingstation 10 is placed in the pulmonary artery, which is a large vessel,the significant volume of blood flowing through the artery is funneledinto the valve 29 by the cloth covering 21. The cloth 21 is fluidimpermeable so that blood cannot pass through. Again, a variety of otherbiocompatible covering materials may be used such as, for example, foamor a fabric that is treated with a coating that is impermeable to blood,polyester, or a processed biological material, such as pericardium.

In the example illustrated by FIG. 21, more of the docking station frame1500 is provided with the impermeable material 21, forming a relativelylarge impermeable portion 1404. In the example illustrated by FIG. 21,the impermeable portion 1404 extends from the inflow end 12 and stopsone row of cells 1504 before the outflow end. As such, the most distalrow of cells 1504 form a permeable portion 1400. However, more rows ofcells 1504 can be uncovered by the impermeable material to form a largerpermeable portion. The permeable portion 1400 allows blood to flow intoand out of the area 2130 as indicated by arrows 2132. With respect tothe inflow end 12, it should be noted that since the cells 1504 aregenerally diamond shaped, blood is able to flow between the dockingstation 10 and the surface 416, until the sealing portion 410 isreached. That is, blood can flow into and out of the areas 2100 in oneexemplary embodiment.

The valve seat 18 can provide a supporting surface for implanting ordeploying a valve 29 in the docking station 10. The retaining portions414 can retain the docking station 10 at the implantation position ordeployment site in the circulatory system. The illustrated retainingportions have an outwardly curving flare that helps secure the dockingstation 10 within the artery. “Outwardly” as used herein means extendingaway from the central longitudinal axis of the docking station. As canbe seen in FIG. 20, when the docking station 10 is compressed by theinside surface 416, the retaining portions 414 engage the surface 416 atan angle α (normal to the surface to the tangent of the midpoint of thesurface of the retaining portion 414) that can be between 30 and 60degrees, such as about 45 degrees, rather than extending substantiallyradially outward (i.e. a is 0 to 20 degrees or about 10 degrees) as inthe uncompressed condition (See FIG. 15B). This inward bending of theretaining portions 414 as indicated by arrow 2020 acts to retain thedocking station 10 in the circulatory system. The retaining portions 14are at the wider inflow end portion 12 and outflow end portion 14 andpress against the inner surface 416. The flared retaining portions 414engage into the surrounding anatomy in the circulatory system, such asthe pulmonic space. In one exemplary embodiment, the flares serve as astop, which locks the device in place. When an axial force is applied tothe docking station 10, the flared retaining portions 414 are pushed bythe force into the surrounding tissue to resist migration of the stentas described in more detail below. In a specific embodiment, the dockingstation generally has an hourglass shape, with wider distal and proximalend portions that have the flared retaining portion and a narrow, bandedwaist in between the ends, into which the valve is expanded.

FIG. 22 illustrates the docking station 10 deployed in the circulatorysystem and a valve 29 deployed in the docking station 10. After thedocking station 10 is deployed, the valve 29 is in a compressed form andis introduced into the valve seat 18 of the docking station 10. Thevalve 29 is expanded in the docking station, such that the valve 29engages the valve seat 18. In the example illustrated by FIG. 22, thedocking station 10 is longer than the valve. However, in one embodiment,the docking station 10 may be the same length or shorter than the lengthof the valve 10.

The valve 29 may be delivered to the site of the docking station viaconventional means, such as by balloon or mechanical expansion or byself-expansion. When the valve 29 is expanded, it nests in the valveseat of the docking station 10. In one embodiment, the banded waist isslightly elastic and exerts an elastic force against the valve 29, tohelp hold the THV in place.

FIGS. 23A and 23B illustrate that the docking station 10 can be used toadapt a variety of different sizes of circulatory system anatomies forimplantation of a valve 29 having a consistent size. In the example ofFIGS. 23A and 23B, the same size docking station 10 is deployed in twodifferent sized vessels 2300, 2302, such as two differently sizedpulmonary arteries PA. In the example, the vessel 2300 illustrated byFIG. 23A has a larger effective diameter than the vessel 2302illustrated by FIG. 23B. (Note that in this patent application the sizeof the anatomy of the circulatory system is referred to by the term“diameter” or “effective diameter.” The anatomy of the circulatorysystem is often not circular. The terms “diameter” and “effectivediameter” herein refers to the diameter of a circle or disc that couldbe deformed to fit within the non-circular anatomy.) In the exampleillustrated by FIGS. 23A and 23B, the sealing portion 410 and theretaining portions 414 conform to contact each vessel 2300, 2302.However, the valve seat 18 remains the same size, even though thesealing portion 410 and the retaining portions 414 are compressed. Inthis manner, the docking station 10 adapts a wide variety of differentanatomical sizes for implantation of a standard or single sized valve.For example, the docking station may conform to vessel diameters of 25mm and 40 mm, such as 27 mm and 38 mm and provide a constant orsubstantially constant diameter valve seat of mom to 30 mm, such as 27mm to 28 mm. However, the valve seat 10 can be adapted for applicationswhere the vessel diameter is larger or smaller than 25 mm to 40 mm andprovide valve seats that are larger or smaller than mom to 30 mm.

Referring to FIGS. 23A and 23B, a band 20 maintains a constant orsubstantially constant diameter of the valve seat 18, even as theproximal and distal ends of the docking station expand to respectivediameters necessary to engage with the inside surface 416. The diameterof the pulmonary artery PA can vary considerably from patient topatient, but the valve seat 18 in the deployed configurationconsistently has a diameter that is within an acceptable range for thevalve 29.

FIGS. 24 and 25 illustrate side profiles of the docking station 10illustrated by FIG. 18 when implanted in different sized vessels 2300,2302 of the circulatory system with a schematically illustratedtranscatheter heart valve 29 having the same size installed or deployedin each docking station 10. In this example, the docking station 10 bothaccommodates vessels 2300, 2302 having a variety of different sizes andacts as an isolator that prevents or substantially prevents radialoutward forces of the valve 29 from being transferred to the vessels.The valve seat 18 is not expanded radially outwardly or is notsubstantially expanded radially outward by the radially outward force ofthe valve 29 and the anchoring/retaining portions 414 and the sealingportions 410 impart only relatively small radially outward force on thevessels 2300, 2302 (as compared to the radially outward force applied tothe valve seat 18 by the valve 29), even when the docking station isdeployed in a vessel 2302 having a smaller diameter.

In the example illustrated by FIGS. 24 and 25, the stent or frame 712 ofthe valve 29 expands radially outward or is expanded radially outward toimport the high force 710 on the valve seat 18 of the docking station10. This high radially outward force 710 secures the valve 29 to thevalve seat 18 of the docking station 10. However, since the valve seat18 is not expanded or is not substantially expanded by the force 710,the force 710 is isolated from the circulatory system, rather than beingused to secure the docking station in the circulatory system.

In an exemplary embodiment, the radially outward force 722 of thesealing portions 410 to both the larger vessel 2300 and the smallervessel is substantially smaller than the radially outward force 710applied by the valve 29 to the valve seat 18. For example, for thesmallest vessel to be adapted by the docking station 10 for valveimplantation, the radially outward sealing force 722 can be less than ½the radially outward force 710 applied by the valve, less than ⅓ theradially outward force 710 applied by the valve, less than ¼ theradially outward force 710 applied by the valve, less than ⅛, or evenless than 1/10 the radially outward force 710 applied by the valve. Inone exemplary embodiment, the radially outward force 722 of the sealingportions 410 is selected to provide a seal between the inner surface 416and the sealing portion 410, but is not sufficient by itself to retainthe position of the valve 29 and docking station 10 in the circulatorysystem. In one embodiment, the radially outward force 722 is sufficientto retain the position of the valve 29 and docking station 10 in thecirculatory system.

In an exemplary embodiment, the docking station 10 illustrated by FIG.18 also includes anchoring/retaining portions 414 that apply radiallyoutward forces 720 that are substantially smaller than the radiallyoutward force 710 applied by the valve 29 to the valve seat 18. Forexample, for the smallest vessel to be adapted by the docking station 10for valve implantation, the radially outward sealing force 720 can beless than ½ the radially outward force 710 applied by the valve, lessthan ⅓ the radially outward force 710 applied by the valve, less than ¼the radially outward force 710 applied by the valve, less than ⅛, oreven less than 1/10 the radially outward force 710 applied by the valve.In one embodiment, the radially outward force 720 of theanchoring/retaining portions 414 is not sufficient by itself to retainthe position of the valve 29 and docking station 10 in the circulatorysystem. In one embodiment, the radially outward force 720 is sufficientto retain the position of the valve 29 and docking station 10 in thecirculatory system.

In one exemplary embodiment, the docking station 10 frame 1500 is madefrom an elastic or superelastic material or metal. One such metal isnitinol. When the frame 1500 of the docking station 10 is made from alattice of metal struts, the body can have the characteristics of aspring. Referring to FIG. 7C, like a spring, when the frame 1500 of thedocking station 10 illustrated by FIGS. 24 and 25 is unconstrained andallowed to relax to its largest diameter the frame of the dockingstation applies little or no radially outward force. As the frame 1500of the docking station 10 is compressed, like a spring, the radiallyoutward force applied by the docking station increases. As isillustrated by FIG. 7C, in one exemplary embodiment the relationship ofthe radially outward force of the docking station frame 1500 to theexpanded diameter of the docking station is non-linear, though it canalso be linear. In the example illustrated by FIG. 7C, the curve 750illustrates the relationship between the radially outward force exertedby the docking station 10 and the compressed diameter of the dockingstation. In the region 752, the curve 750 has a low slope. In thisregion 752 the radially outward force is low and changes only a smallamount. In one exemplary embodiment, the region 752 corresponds to adiameter between 25 mm and 40 mm, such as between 27 mm and 38 mm. Theradially outward force is small in the region 752, but is not zero. Inthe region 754, the curve 750 has a higher slope. In this region 754 theradially outward force increases significantly as the docking station iscompressed. In one exemplary embodiment, the body of the stent isconstructed to be in the low slope region 752 for both a largest vessel2300 (FIG. 24) accommodated by the docking station 10 and a smallestvessel 2302 (FIG. 25). This allows the sealing portions 710 to applyonly a small radially outward force to the inner surface 416 of thecirculatory system over a wide range of diameters.

FIGS. 26A-26C illustrate the docking station 10 of FIG. 18 implanted ina pulmonary artery. FIG. 26A illustrates the profile of the dockingstation 10 implanted in the pulmonary artery PA. FIG. 26B illustratesthe profile of the docking station 10 implanted in the pulmonary arteryPA with a schematically illustrated valve 29 installed or deployed inthe docking station 10. FIG. 26C illustrates the docking station 10 andvalve 29 as depicted in FIG. 22 implanted in the pulmonary artery PA. Asmentioned with respect to FIGS. 2A-2E and 3A-3D, the shape of thepulmonary artery may vary significantly along its length. In oneexemplary embodiment, the docking station 10 is configured to conform tothe varying shape of the pulmonary artery PA. The docking station 10 isillustrated as being positioned below the pulmonary artery bifurcationor branch. However, often the docking station 10 will be positioned suchthat the end 14 extends into the pulmonary artery bifurcation 210. Whenit is contemplated that the docking station 10 will extend into thepulmonary artery bifurcation, the docking station 10 can have a bloodpermeable portion 1400 (e.g., as shown in FIG. 21).

FIG. 27 illustrates another exemplary embodiment of a docking station10. The docking station 10 includes a frame 2700 and an external sealingportion 410. The frame 2700 or body can take a wide variety of differentforms and FIG. 27 illustrates just one of the many possibleconfigurations. In the example illustrated by FIG. 27 the dockingstation 10 has a relatively wider proximal inflow end 12 and distaloutflow end 14, and an elongated relatively narrower portion 2716. Theseat 18 and sealing portion 410 can be provided anywhere along thelength of the elongated relatively narrow portion 2716. In the exampleillustrated by FIG. 27, the frame 2700 of the docking station 10 ispreferably a stent comprised of a plurality of metal struts 1502 thatform cells 1504. The frame 2700 or portion(s) of the frame canoptionally be covered by an impermeable material 21 (e.g., as shown inFIG. 18).

FIG. 27 illustrates the frame 2700 and sealing portion 410 in theirunconstrained, expanded condition/configuration or deployedconfiguration. In this exemplary embodiment, the retaining portions 414comprise ends 1510 of the metal struts 1502 at the proximal and distalends 12, 14. The sealing portion 410 can be a separate component that isdisposed around the frame 2700 between the retaining portions 414. Inthe unconstrained condition, the retaining portions 414 extend generallyradially outward and may be radially outward of the sealing portion 410.

The docking station 10 illustrated by FIG. 27 may be made from a veryresilient or compliant material to accommodate large variations in theanatomy. For example, the docking station may be made from a highlyflexible metal (e.g., the frame in the FIG. 27 example) and cloth and/oran open cell foam (e.g., the sealing portion in the FIG. 27 example). Anexample of a highly resilient metal is nitinol, but other metals andhighly resilient or compliant non-metal materials can be used. Anexample of an open cell foam that can be used is a biocompatible foam,such as a polyurethane foam (e.g., as may be obtained from Biomerix,Rockville, Md.). In one embodiment, a foam forming the sealing portionmay also form a valve seat on its inner surface.

Still referring to FIG. 27, the frame 2700 and/or the separate sealingportion 410 may include an optional a band 20 to form an unexpandable orsubstantially unexpandable valve seat 18. In another exemplaryembodiment, the frame 2700 may be configured to be substantiallyunexpandable in the area of the valve seat 18 without the use of a band20. The optional band 20 stiffens the frame 2700 and/or sealing portionand makes the valve seat relatively unexpandable.

The optional band 20 can take a wide variety of different forms, can bemade from a wide variety of different materials, and can be the same asor similar to bands discussed elsewhere in this disclosure. The band 20can be made of PET, one or more sutures, fabric, metal, polymer, abiocompatible tape, or other relatively unexpandable materials known inthe art that are sufficient to maintain the shape of the valve seat 18and hold the valve 29 in place. The band can extend about the exteriorof the stent, or can be an integral part of it, such as when fabric oranother material is interwoven into or through cells of the stent. Theband 20 can be narrow, such as the suture band in FIG. 18, or can bewider as illustrate by the dashed line in FIG. 27. In one non-limitingexample, the valve seat 18 is between 27-28 mm in diameter, although thediameter of the valve seat should be within the operating range of theparticular valve 29 that will be secured within the valve seat 18, andmay be different than the foregoing example.

FIGS. 28 and 29 illustrate a modified version of the docking station 10illustrated by FIG. 27 that is expandable in length. As mentioned above,the length of the pulmonary artery PA and other anatomical structures ofthe circulatory system may vary greatly from patient to patient.Referring to FIG. 29, in one exemplary embodiment the length of thedocking station 10 is adjustable as indicated by arrow 1100. The lengthmay be adjusted in a wide variety of different ways, e.g., it can beadjustable in any of the ways described elsewhere in this disclosure. Inthe example illustrated by FIGS. 28 and 29, the docking station 10includes a first half 1102 and a second half 1104. The second half 1104can be inserted or “telescoped” into the first half 1102. The amount ofinsertion or “telescoping” sets the length of the docking station 10.

In one exemplary embodiment, the length of the docking station 10 isadjusted in the pulmonary artery PA by first deploying the first half1102 of the docking station 10 in the pulmonary artery. For example, thefirst half 1102 may be positioned and expanded such that a distal end1106 of the first half is aligned with or extends somewhat past thebranch of the pulmonary artery. After the first half 1102 is expanded inthe pulmonary artery, the compressed second half 1104 is positioned witha distal end 1110 disposed in the proximal end 1108 of the first half1102. The position of the second half 1104 is selected such that thesealing portion 410 and retaining portion 414 will make contact with thepulmonary artery and set the position of the docking station 10 in thepulmonary artery. Once properly positioned, the second half 1104 isexpanded. The distal end of 1110 of the second half 1104 frictionallyengages the proximal end 1108 of the first half to secure the two halves1102, 1104 together. In one embodiment, a lock(s), locking mechanism,suture(s), interlacing, link(s) and/or other attachment device/mechanismmay (also or alternatively) be used to secure the two halves together.

In the examples illustrated by FIGS. 28 and 29, the seat 18 and thesealing portion 410 are included on the first half 1102 of the dockingstation 10. However, in other embodiments the seat 18 and/or the sealingportion(s) 410 can be included on the second half 1104 or in differentlocations on the first half and/or the second half.

FIGS. 30 and 31A illustrate the docking station 10 of FIG. 27 of FIGS.28 and 29 implanted in the circulatory system, such as in the pulmonaryartery PA. The sealing portion 410 provides a seal between the dockingstation 10 and an interior surface 416 of the pulmonary artery PA. Inthe example of FIGS. 30 and 31A, the sealing portion 410 is an expandingmaterial, such as an expandable open cell foam over the frame 2700. Inan exemplary embodiment, the sealing portion 410 coincides or at leastoverlaps with the valve seat 18. When the sealing portion 410 does notoverlap with the valve seat 18, an impermeable material 21 may beprovided over a portion of the frame (e.g., from the sealing portion 410to the valve seat 18 to make the docking station impermeable from thesealing portion 410 to the valve seal 18). Whether the sealing portion410 overlaps with the valve seat 10 or an impermeable material isprovided from the sealing portion 410 to the valve seat 18, all bloodflowing in the inflow direction 12 toward the outflow direction 14 isdirected to the valve seat 18 (and valve 29 once installed or deployedin the valve seat).

In one exemplary embodiment of a docking station 10, at least theoutflow portion 14 of the frame 2700 is relatively open. Referring toFIG. 31A, this allows the docking station 10 to be placed higher in thepulmonary artery without restricting blood flow. For example, the opencells 1504 may extend into the branch or bifurcation of the pulmonaryartery and not impede or not significantly impede the flow of blood pastthe branch. The open cells 1504 allow blood to flow through the frame1500 as indicated by arrows 3132 in FIG. 31A.

In the example illustrated by FIGS. 30 and 31A, the docking station 10is retained in the pulmonary artery PA by expanding one or more of theretaining portions 414 radially outward into an area 210, 212 of thepulmonary artery PA where the inside surface 416 also extends outward.For example, the retaining portions 414 may be configured to extendradially outward into the pulmonary bifurcation 210 and/or the opening212 of the pulmonary artery to the right ventricle RV. In one exemplaryembodiment, the docking station 10 can be an adjustable docking station.For example, docking station 10 can be a telescoping docking station asillustrated by FIG. 28 and the first portion 1102 is deployed such thatthe retaining portions 414 extend radially outward into the pulmonarybifurcation 210). The second portion 1104 can then be positioned in thefirst portion 1102 such that its retaining portions 414 coincide withthe opening of the pulmonary artery or another outwardly extending areaof the pulmonary artery. Once in position, the second portion 1104 canbe expanded to secure the second section 1104 to the first section 1102and to secure the second section to the pulmonary artery at the opening212 or other outwardly extending area.

Referring to FIG. 31B, the valve seat 18 provides a supporting surfacefor installing or deploying a valve 29 in the docking station 10. Thevalve may be installed or deployed in the valve seat using the stepsdisclosed here or elsewhere in this disclosure. The anchoring/retainingportions 414 retain the docking station 10 at the implantation ordeployed site/position in the circulatory system. After the dockingstation 10 is deployed, the valve 29 is in a compressed form and can beintroduced into the valve seat 18 of the docking station 10. The valve29 can be expanded in the docking station, such that the valve 29engages the valve seat 18. The valve 29 can be delivered to the site ofthe docking station via conventional means, such as by balloon ormechanical expansion or by self-expansion. When the valve 29 isexpanded, it nests in the valve seat of the docking station 10.

Referring to FIG. 32A, the docking station illustrated by FIG. 18 isdeployed in the pulmonary artery PA of a heart H. FIG. 32B illustrates agenerically illustrated valve 29 deployed in the docking station 10illustrated by FIG. 32A. In FIGS. 32A and 32B, the heart is in thesystolic phase. FIG. 33A is an enlarged representation of the dockingstation 10 and valve 29 in the pulmonary artery 29 of FIG. 32B. When theheart is in the systolic phase, the valve 29 opens. Blood flows from theright ventricle RV and through the pulmonary artery PA, docking station10, and valve 29 as indicated by arrows 3202. FIG. 33B illustrates space3208 that represents the valve 29 being open when the heart is in thesystolic phase. FIG. 33B does not show the interface between the dockingstation 10 and the pulmonary artery to simplify the drawing. Thecross-hatching in FIG. 33B illustrates blood flow through the openvalve. In an exemplary embodiment, blood is prevented from flowingbetween the pulmonary artery PA and the docking station 10 by the seal410 and blood is prevented from flowing between the docking station 10and the valve 29 by seating of the valve 29 in the seat 18 of thedocking station 10. In this example, blood is substantially only or onlyable to flow through the valve 29 when the heart is in the systolicphase.

FIG. 34 illustrates the valve 29, docking station 10 and heart Hillustrated by FIG. 32B, when the heart is in the diastolic phase.Referring to FIG. 34, when the heart is in the diastolic phase, thevalve 29 closes. FIG. 35A is an enlarged representation of the dockingstation 10 and valve 29 in the pulmonary artery 29 of FIG. 34. Bloodflow in the pulmonary artery PA above the valve 29 (i.e. in thepulmonary branch 210) is blocked by the valve 29 being closed andblocking blood flow as indicated by arrow 3400. The solid area 3512 inFIG. 35B represents the valve 29 being closed when the heart is in thediastolic phase.

Referring to FIG. 33A, the radially outward force 720 of theanchoring/retaining portions 414 to the inside surface 416 issubstantially smaller than the radially outward force 710 applied by thevalve 29 to the valve seat 18. For example, the radially outward sealingforce 720 can be less than ½ the radially outward force 710 applied bythe valve, less than ⅓ the radially outward force 710 applied by thevalve, less than ¼ the radially outward force 710 applied by the valve,less than ⅛, or even less than 1/10 the radially outward force 710applied by the valve.

Referring to FIGS. 33A and 35A, in one exemplary embodiment the radiallyoutward force 720 of the retaining portions 414 is not sufficient byitself to retain the position of the valve 29 and docking station 10 inthe circulatory system. Rather, the pressure of the blood 3208 is usedto enhance the retention of the retaining portions 414 to the insidesurface 416. Referring again to FIG. 33A, when the heart is in thesystolic phase, the valve 29 is open and blood flows through the valveas indicated by arrows 3202. Since the valve 29 is open and blood flowsthrough the valve 29, the pressure P applied to the docking station 10and valve 29 by the blood is low as indicated by the small P and arrowin FIG. 33A. Even though small, the pressure P forces the dockingstation and its upper retaining portions 414 against the surface 416generally in the direction indicated by arrow F (the small F representsa relatively low force). This blood flow assisted force F applied by theretaining portions F to the surface 416 prevents the docking station 10and valve 29 from moving in the direction 3302 of blood flow in thesystolic phase of the heart H.

Referring to FIG. 35A, when the heart is in the diastolic phase, thevalve 29 is closed and blood flow is blocked as indicated by arrow 3400.Since the valve 29 is closed and the valve 29 and docking station 10block the flow of blood, the pressure P applied to the docking station10 and valve 29 by the blood is high as indicated by the large arrow Pin FIG. 35A. This large pressure P forces the lower retaining portions414 against the surface 416 generally in the direction indicated by thelarge arrows F (the large F represents a relatively larger force). Thisblood flow assisted force F applied by the retaining portions F to thesurface 416 prevents the docking station 10 and valve 29 from moving inthe direction indicated by arrow 3400.

Referring to FIGS. 33A and 35A, since the force applied by the upper andlower retaining portions 414 is determined by amount of pressure appliedto the valve 29 and docking station 10 by the blood, the force appliedto the surface 416 is automatically proportioned. That is, the upperretaining portions are less forcefully pressed against the surface 416when the heart is in the systolic phase than the lower retainingportions are pressed against the surface 416 when the heart is in thediastolic phase. This is because the pressure against the open valve 29and docking station 10 in the systolic phase is less than the pressureagainst the closed valve and docking station in the diastolic phase.

Methods of treating a patient (e.g., methods of treating heart valvedysfunction/regurgitation/etc.) may include a variety of steps,including steps associated with introducing and deploying a dockingstation in a desired location/treatment area and introducing anddeploying a valve in the docking station. For example, FIG. 36Aillustrates the docking station illustrated by FIG. 18 being deployed bya catheter 3600. The docking station 10 can be positioned and deployedin a wide variety of different ways. Access can be gained through thefemoral vein or access can be percutaneous. Generally, any vascular paththat leads to the pulmonary artery may be used. In one exemplaryembodiment, a guidewire followed by a catheter 3600 is advanced to thepulmonary artery PA by way of the femoral vein, inferior vena cava,tricuspid valve, and right ventricle RV. The docking station 10 can beplaced in the right ventricular outflow tract/pulmonary artery PA tocreate an artificial conduit and landing zone for a valve (e.g., atranscatheter heart valve) 29.

Referring to FIG. 36B, the docking station illustrated by FIG. 18 isdeployed in the pulmonary artery (PA) of a heart H. FIG. 36C illustratesa valve 29 deployed in the docking station 10 illustrated by FIG. 32A.In the example illustrated by FIGS. 36C, 37A, 38, 39A, and 39B, thevalve 29 is depicted as a SAPIEN 3 THV provided by Edwards Lifesciences;however, a variety of other valves may also be used. In FIGS. 36A-36C,the heart is in the systolic phase. FIG. 37A is an enlargedrepresentation of the docking station 10 and valve 29 in the pulmonaryartery 29 of FIG. 36C. When the heart is in the systolic phase, thevalve (e.g., Sapien 3 valve) is open. Blood flows from the rightventricle RV and through the pulmonary artery PA, docking station 10,and valve as indicated by arrows 3202. FIG. 37B illustrates space 3208that represents the valve being open when the heart is in the systolicphase. FIG. 37B does not show the interface between the docking station10 and the pulmonary artery to simplify the drawing. The cross-hatchingin FIG. 37B illustrates blood flow through the valve. In an exemplaryembodiment, blood is prevented from flowing between the pulmonary arteryPA and the docking station 10 by the seal 410 and blood is preventedfrom flowing between the docking station 10 and the valve by seating ofthe valve in the seat 18 of the docking station 10. In this example,blood is substantially only or only able to flow through the valve whenthe heart is in the systolic phase.

FIG. 38 illustrates the valve 29, docking station 10 and heart Hillustrated by FIG. 36C, when the heart is in the diastolic phase.Referring to FIG. 38, when the heart is in the diastolic phase, thevalve 29 closes. FIG. 39A is an enlarged representation of the dockingstation 10 and valve (e.g., Sapien 3 valve) in the pulmonary artery 29of FIG. 38. Blood flow in the pulmonary artery PA above the valve 29(i.e. in the pulmonary branch 210) is blocked by the valve 29 beingclosed and blocking blood flow as indicated by arrow 3400. The solidarea 3512 in FIG. 39B represents the valve 29 being closed when theheart is in the diastolic phase.

Referring to FIG. 39A, the radially outward force 720 of theanchoring/retaining portions 414 to the inside surface 416 issubstantially smaller than the radially outward force 710 applied by thevalve (e.g., Sapien 3 valve) to the valve seat 18. For example, theradially outward sealing force 720 can be less than ½ the radiallyoutward force 710 applied by the valve, less than ⅓ the radially outwardforce 710 applied by the valve, less than ¼ the radially outward force710 applied by the valve, less than ⅛, or even less than 1/10 theradially outward force 710 applied by the valve. The 29 mm size Sapien 3valve typically applies radially outward force 710 of about 42 Newtons.In one embodiment, the radially outward force of deployed dockingstations described herein or one or more portions of a deployed dockingstations can be between about 4 to 16 Newtons, though other forces arealso possible.

FIG. 40A illustrates the docking station illustrated by FIG. 27 or 28being deployed by a catheter 3600. Referring to FIG. 40B, the dockingstation illustrated by FIG. 27 or 28 is deployed in the pulmonary arteryPA of a heart H. FIG. 40C illustrates a valve 29 deployed in the dockingstation 10 illustrated by FIG. 40A. In the example illustrated by FIGS.36C, 37A, 38, 39A, and 39B, the valve 29 is a SAPIEN 3 THV provided byEdwards Lifesciences, though a variety of different valves may be used.In FIGS. 40A-40C, the heart is in the systolic phase. FIG. 41A is anenlarged representation of the docking station 10 and valve 29 in thepulmonary artery 29 of FIG. 40C. When the heart is in the systolicphase, blood flows from the right ventricle RV and through the pulmonaryartery PA, docking station 10, and valve 29 as indicated by arrows 3202.FIG. 41B illustrates space 3208 that represents the valve 29 being openwhen the heart is in the systolic phase. FIG. 41B does not show theinterface between the docking station 10 and the pulmonary artery tosimplify the drawing. The cross-hatching in FIG. 41B illustrates bloodflow through the valve 29. In an exemplary embodiment, blood isprevented from flowing between the pulmonary artery PA and the dockingstation 10 by the seal 410 and blood is prevented from flowing betweenthe docking station 10 and the valve 29 by seating of the valve in theseat 18 of the docking station 10. In this example, blood issubstantially only or only able to flow through the valve when the heartis in the systolic phase.

FIG. 42 illustrates the valve 29, docking station 10 and heart Hillustrated by FIG. 40C, when the heart is in the diastolic phase.Referring to FIG. 42, when the heart is in the diastolic phase, thevalve 29 closes. FIG. 43A is an enlarged representation of the dockingstation 10 and valve 29 in the pulmonary artery 29 of FIG. 42. Bloodflow in the pulmonary artery PA above the valve 29 (i.e. in thepulmonary branch 210) is blocked by the valve 29 being closed andblocking blood flow as indicated by arrow 3400. The solid area 3512 inFIG. 43B represents the valve 29 being closed when the heart is in thediastolic phase.

Referring to FIG. 43A, the docking station 10 is retained in thepulmonary artery PA by expanding one or more of the retaining/anchoringportions 414 radially outward into an area 210, 212 of the pulmonaryartery PA where the inside surface 416 also extends outward. Forexample, the retaining portions 414 may be configured to extend radiallyoutward into the pulmonary bifurcation 210 and/or the opening 212 of thepulmonary artery to the right ventricle RV. In one exemplary embodiment,the docking station 10 can be an adjustable and/or multiple componentdocking station. For example, docking station 10 can be a telescopingdocking station as illustrated by FIG. 28 and the first portion 1102 canbe deployed such that the retaining portions 414 extend radially outwardinto the pulmonary bifurcation 210 and the second portion 1104 can bepositioned in the first portion 1102 such that its retaining portions414 coincide with the opening 212 of the pulmonary artery. The extensionof the retaining portions 414 into the areas 210, 212 set the positionof the docking station 10 in the pulmonary artery PA and help preventthe pressure P shown in FIG. 43A from moving the docking station.

The valve 29 used with the docking station 10 can take a wide variety ofdifferent forms. In one exemplary embodiment, the valve 29 is configuredto be implanted via a catheter in the heart H. For example, the valve 29may be expandable and collapsible to facilitate transcatheterapplication in a heart. However, in other embodiments, the valve 29 maybe configured for surgical application. Similarly, the docking stationsdescribed herein may be placed using transcatheter application/placementor surgical application/placement.

FIGS. 44-48 illustrate a few examples of the many valves or valveconfigurations that can be used. Any valve type may be used and somevalves that are traditionally applied surgically may be modified fortranscatheter implantation. FIG. 44 illustrates an expandable valve 29for transcatheter implantation that is shown and described in U.S. Pat.No. 8,002,825, which is incorporated herein by reference in itsentirety. An example of a tri-leaflet valve is shown and described inPublished Patent Cooperation Treaty Application No. WO 2000/42950, whichis incorporated herein by reference in its entirety. Another example ofa tri-leaflet valve is shown and described in U.S. Pat. No. 5,928,281,which is incorporated herein by reference in its entirety. Anotherexample of a tri-leaflet valve is shown and described in U.S. Pat. No.6,558,418, which is incorporated herein by reference in its entirety.FIGS. 45-47 illustrate an exemplary embodiment of an expandabletri-leaflet valve 29, such as the Edwards SAPIEN Transcatheter HeartValve. Referring to FIG. 45, in one exemplary embodiment the valve 29comprises a frame 712 that contains a tri-leaflet valve 4500 (See FIG.46) compressed inside the frame 712. FIG. 46 illustrates the frame 712expanded and the valve 29 in an open condition. FIG. 47 illustrates theframe 712 expanded and the valve 29 in a closed condition. FIGS. 48A,48B, and 48C illustrate an example of an expandable valve 29 that isshown and described in U.S. Pat. No. 6,540,782, which is incorporatedherein by reference in its entirety. An example of a valve is shown anddescribed in U.S. Pat. No. 3,365,728, which is incorporated herein byreference in its entirety. Another example of a valve is shown anddescribed in U.S. Pat. No. 3,824,629, which is incorporated herein byreference in its entirety. Another example of a valve is shown anddescribed in U.S. Pat. No. 5,814,099, which is incorporated herein byreference in its entirety. Any of these or other valves may be used asvalve 29 in the various embodiments disclosed herein.

FIGS. 49A, 49B and 50A-50D illustrate a distal portion of an exemplaryembodiment of a catheter 3600 for delivering and deploying the dockingstation 10. The catheter 3600 can take a wide variety of differentforms. In the illustrated example, the catheter 3600 includes an outertube/sleeve 4910, an inner tube/sleeve 4912, a docking station connector4914 that is connected to the inner tube 4912, and an elongated nosecone28 that is connected to the docking station connector 4914 by aconnecting tube 4916.

The docking station 10 can be disposed in the outer tube/sleeve 4910(See FIG. 49B). Elongated legs 5000 can connect the docking station 10to the docking station connector 4914 (See FIG. 49B). The elongated legs5000 can be retaining portions that are longer than the remainder of theretaining portions 414. The catheter 3600 can be routed over a guidewire5002 to position the docking station 10 at the delivery site.

Referring to FIGS. 50A-50D, the outer tube 4910 is progressivelyretracted with respect to inner tube 4912, the docking station connector4914, and the elongated nosecone 28 to deploy the docking station 10. InFIG. 50A, the docking station 10 begins to expand from the outer tube4910. In FIG. 50B, a distal end 14 of the docking station 10 expandsfrom the outer tube 4910. In FIG. 50C, the docking station 10 isexpanded out of the outer tube, except the elongated legs 5000 remainretained by the docking station connector 4914 in the outer tube 4910.In FIG. 50D, docking station connector 4914 extends from the outer tube4910 to release the legs 5000, thereby fully deploying the dockingstation. During deployment of a docking station in the circulatorysystem, similar steps may be used and the docking station may bedeployed in a similar way.

FIGS. 51 and 54 illustrate exemplary embodiments of the nosecone 28. Inone exemplary embodiment, the nosecone 28 is an elongated flexible tipor distal end 5110 on a catheter used to assist feeding the catheter3600 into the heart. In the illustrated examples, nosecone 28 is a long,gradually-tapering cone, with the narrow, distal end of the cone beingrelatively flexible. In one non-limiting embodiment, a nosecone has alength of 1.5 inches, with an inner lumen 5200 of the nosecone 28 havingan inner diameter of 0.04 inches to accommodate the guidewire 5002. Inone embodiment, as the diameter of the nosecone 100 increases from thenarrow distal end to the wider proximal end, the cone becomes graduallymore stiff. This may be due to the increase in thickness and/or thenosecone may be constructed from different materials having differentdurometers. Optionally, the stiffness of the nose cone at the point itconnects with the outer tube 4910 may be approximately the same as thestiffness of the outer tube 4910, in order to prevent a sudden change instiffness. In the examples illustrated by FIGS. 51 and 54, the elongateddistal ends 5110 of the nosecone 28 are the same. In one embodiment, thetaper of the nosecone 28 extends the full length or only a portion ofthe length of the nosecone 28 from end to end. To form the taper anouter diameter of the nosecone 28 can increase in a distal to proximaldirection. The taper can take a variety of shapes and the outer surfaceof the taper can be at a variety of angles with respect to alongitudinal axis of the nosecone 28.

In one exemplary embodiment, a longer distal end 5110 of the nosecone 28assists in navigating around a bend or curve in the patient'svasculature. Because of the increased length of the nosecone 28 more ofthe tip gets around the bend, and creates a “follow-the-leader” effectwith the remainder of the nose cone.

In the example illustrated by FIG. 51, the base or proximal end 5112 ofthe nosecone 28 has a proximal angled portion 5308 adjacent to a shelf5310. The proximal angled portion does not catch on the docking station10 that has been implanted in the heart, when the delivery catheter isretrieved. Thus, the proximal base portion 5112 allows for easierremoval of the delivery system. Referring to FIG. 53, as the angledportion 5308 (or “ramp”) of the base portion 5112 is retracted into theouter tube 4910, the ramp 5308 enters the delivery catheter first,followed by the shelf 5310. When the nose cone 28 engages with the outersleeve/tube 4910, the inner diameter of the outer sleeve rides up theramp 5308, and then rests on the shelf 5310 (which can be flat orsubstantially flat, e.g., 180° or 180°±5° with respect to a longitudinalaxis of the nosecone 28). The inner diameter of the outer sleeve/tube4910 can be slightly less than the diameter of the shelf 5310, to ensurea snug fit.

In one non-limiting example, the shelf 5310 of the nosecone 28 fitssnugly into a lumen or outer lumen of the catheter assembly 3600 which,in one non-limiting example, can have a diameter of approximately 0.2inches or between 0.1 inches and 0.4 inches. In one embodiment, theouter diameter of the largest portion of the nosecone 28 can be 0.27inches or between 0.2 inches and 0.4 inches, with a diameter at thedistal tip of the nosecone of 0.069 inches or between 0.03 inches and0.1 inches. Again, these dimensions are for illustrative purposes only.For example, the outer diameter or largest outer diameter of thenosecone 28 can be larger than the outer diameter of the outer tube 4910(e.g., slightly larger as illustrated), the outer diameter of thenosecone 28 can be the same as the outer diameter of the outer tube4910, or the outer diameter of the nosecone 28 can be smaller (e.g.,slightly smaller) than the outer diameter of the outer tube 4910.

In the example illustrated by FIG. 54, the entire base or proximalend/portion 5112 of the nosecone 28 is angled. The continuously angledproximal end 5112 does not catch on the docking station 10 that has beenimplanted in the heart, when the delivery catheter is retrieved. Thus,the base portion 5112 allows for easier removal of the delivery system.Referring to FIG. 55, the outer tube 4910 may include a chamfer 5500 toaccept and mate with the continuously angled proximal end 5112.

In one non-limiting example, the continuously angled proximal end 5112of the nosecone 28 fits snugly into the outer tube/sleeve 4910 (whichcan optionally be chamfered) of the catheter assembly 3600. The outerdiameter or largest outer diameter of the nosecone 28 can be larger(e.g., slightly larger) than the outer diameter of the outer tube 4910,the outer diameter of the nosecone 28 can be the same as the outerdiameter of the outer tube 4910 as illustrated, or the outer diameter ofthe nosecone 28 can be smaller (e.g., slightly smaller) than the outerdiameter of the outer tube 4910.

The docking station 10 can be coupled to the catheter assembly, or adocking station connector 4914 of the catheter assembly, in a widevariety of different ways. For example, the docking station 10 could becoupled with the catheter assembly with a lock(s), locking mechanism,suture(s) (e.g., one or more sutures releasably attached, tied, or woventhrough one or more portion of the docking station), interlockingdevice(s), a combination of these, or other attachment mechanisms. Someof these coupling or attachment mechanisms may be configured to allowfor the docking station to be retracted back into the catheter assemblywithout causing the docking station to catch on edges of the catheterassembly, e.g., by constraining the proximal end of the docking stationto a smaller profile or collapsed configuration, to allow foradjustment, removal, replacement, etc. of the docking station. FIGS. 56,57, 57A, and 57B illustrate one non-limiting example of how dockingstation 10 may be coupled to the docking station connector 4914. As isillustrated by FIGS. 50A-50D, when the docking station 10 is pushed outof the outer tube, it self-expands in one exemplary embodiment. Oneapproach to controlling expansion of the docking station 10 is to anchorat least one end, such as the proximal end 12, of the stent to thedocking station connector 4914. This approach allows a distal end 14 ofthe stent to expand first, without the proximal end expanding (See FIG.50B). Then when the stent is moved relatively forward with respect tothe outer tube 4910, the proximal end 12 disengages from the dockingstation connector 4914, and the proximal end 12 of the docking stationis permitted to expand (See FIG. 50D).

One way of accomplishing this approach is to include one or moreextensions 5000 on at least the proximal end of the stent 12. In theillustrated examples, two extensions are included. However, any numberof extensions 5000, such as two, three, four, etc. can be included. Theextensions 5000 can take a wide variety of different forms. Theextensions 5000 can engage with the docking station connector 4914within the outer tube 4910. In one exemplary embodiment, the dockingstation connector 4914 may engage an inner face 5600 of the extensions5000. In one exemplary embodiment, other than possible engagement of aninner face 5600 (See FIG. 57A) of the extensions 5000 with the dockingstation connector 4914, the extensions 5000 and docking stationconnector 4914 are configured to limit the retaining engagementtherebetween to two points when the distal portion of the catheterassembly and/or docking station are in a straight or substantiallystraight configuration, but these could similarly be configured to limitthe retaining engagement another number of points, e.g., three to sixpoints. In one exemplary embodiment, the inner face 5600 of theextensions 5000 do not contact with the docking station connector 4914when the distal portion of the catheter assembly and/or the dockingstation is in a straight or substantially straight configuration, due tothe radially outward biasing force of the compressed extensions. In thisembodiment, the inner face 5600 of the extensions 5000 could contact thedocking station connector 4914 due to bending of the catheter assembly3600 and/or the docking station. The extensions 5000 may include heads5636 with sides 5640 that extend away from a straight portion 5638 at anangle β (See FIG. 57A), such as between 30 and 60 degrees. Such heads5636 may be generally triangular as illustrated or the angularlyextending sides 5640 may be connected together by another shape, such asa rounded shape, a rectangular shape, pyramidal shape, or another shape.That is, the heads 5636 may function in the same manner as theillustrated triangular head, without being triangular.

The delivery catheter 3600 constantly bends and curves as it movedthrough the vasculature of the patient's body. A head 5636 thattransitions directly from an straight portion 5638 of the extension 5000to a T-shape, curved T-shaped, circular or spherical shape willgenerally have more than two point retaining contact with its holder(other than possible engagement of an inner face 5600 (See FIG. 17A) ofthe extension 5000 with the docking station connector 4914). Referringto FIGS. 57A and 57B, a head 5636 with sides 5640 that extend away fromone another at an angle β, such as a triangular head, results in thehead 5636 only touching the docking station connector 4914 at two points5702, 5704. In the example illustrated by FIG. 57A, the two points arecorners formed by a T-shaped recess 5710. As shown in FIG. 57B, theextension 5000 can tilt as the catheter 3600 and docking station 10moves through the body during delivery. In one exemplary embodiment,this tilting can also result in only two point contact between theextension 5000 and the docking station connector 4914 as illustrated byFIG. 57B (other than possible engagement of an inner face 5600 (See FIG.17A) of the extension 5000 with the docking station connector 4914). Assuch, the extension 5000 can tilt during delivery, increasing theflexibility of the catheter 3600 in the area of the docking station 10,while the two point contact prevents binding between the extension 5000and the connector 4914.

Referring to FIGS. 56, 57, 57A, and 57B, the heads 5636 fit into theT-shaped recesses 5710 in a holder to holds the proximal end 12 of thedocking station while the distal end self-expands within the body. Thedocking station connector 4914 remains in the delivery catheter untilmoved relatively out of the catheter (i.e. by retracting the outertube/sleeve 4910 or by advancing the connector 4914, See FIG. 50D).Referring to FIG. 56, the outer tube/sleeve 4910 of the catheter 3600can be closely disposed over the connector 4914, such that the heads5636 are captured in the recesses 5710, between the outer tube/sleeve4910 and the body of the connector 4914. This capturing in the recesses5710 holds the end of the docking station 10 as the docking stationexpands. In this manner, delivery of the docking station 10 iscontrolled.

Referring back to FIG. 50D, at the end of the expansion of the dockingstation 10—when the distal end of the stent has already expanded—theconnector 4914 is moved relatively out of the outer sleeve. The heads5636 are then free to move radially outward and disengage with therespective recesses 5710 (see FIG. 56).

In one embodiment, all of the extensions 5000 are the same length. Asthe connector is moved relatively out of the outer tube/sleeve 4910, therecesses 5710 are simultaneously relatively moved out of the outersleeve 4910. Since the extensions 5000 are all the same length, therecesses 5710 with the heads 5636 will all emerge from the deliveryouter sleeve 4910 at the same time. Consequently, the heads 5636 of thedocking station will move radially outward and release all at once.

In an alternative embodiment, the docking station 10 is provided withextensions 5000 having heads 5636, but at least some of the extensions5000 are longer than others. That way, as the connector 4914 isgradually moved relatively out of the outer sleeve 4910, the shortestextensions 5000 are released first from their respective recess(es)5710. Then, as the connector 4914 is moved relatively further out of theouter sleeve 4910, the longer of the extensions 5000 are released fromthe respective recess(es) 5710. As is described above, in one exemplaryembodiment the docking station 10 can be deployed with acatheter/catheter assembly 3600. The catheter/catheter assembly 3600 isadvanced in the circulatory system to a delivery site or treatment area.Once at the delivery site, the docking station 10 is deployed by movingan outer sleeve or tube 4910 relative to an inner sleeve or tube 4912and attached connector 4914 and docking station 10 (See FIGS. 50A-50D).The outer sleeve 4910 can be moved relative to the inner sleeve 4912 ina wide variety of different ways. FIGS. 58-61 and 62-73 illustrateexamples of tools or handles 5800, 6200 that can be used for moving acatheter 3600 in the circulatory system and relatively moving an outersleeve 4910 relative to an inner sleeve 4912 of the catheter 3600, e.g.,to deploy/place a docking station.

In the example illustrated by FIGS. 58-61, the handle 5800 includes ahousing 5810, a drive member 5812, and a driven shaft 5814. In theillustrated example, rotation of the drive member 5812 as indicated byarrow 5816 relative to the housing 5810 moves the driven shaft 5814linearly as indicated by arrow 5818. Referring to FIG. 60, the innersleeve 4912 is fixedly connected to the housing 5810 as indicated byarrow 6000 and the outer sleeve 4910 is fixedly connected to the drivenshaft 5814 as indicted by arrow 6002. As such, rotating the drive member5812 in a first direction retracts the outer sleeve 4910 relative to theinner sleeve 4912 and rotating the drive member 5812 in the oppositedirection advances the outer sleeve 4910 relative to the inner sleeve4912.

In the example illustrated by FIGS. 58-61, the housing 5810 includes anannular recess 5820. The drive member 5812 includes an annularprojection 5822. The annular projection 5822 fits within the annularrecess to rotatably couple the drive member 5812 to the housing 5810.The drive member 5812 includes an engagement portion 5830 that extendsfrom the housing to allow a user to rotate the drive member 5812relative to the housing 5810.

In the example illustrated by FIGS. 58-61, the housing 5810 includes alinear recess 5840 or groove (See FIG. 59). The driven shaft 5814includes a linear projection 5842. The linear projection 5842 fitswithin the linear recess 5840 to slideably couple the driven shaft 5814to the housing 5810.

In the example illustrated by FIGS. 58-61, the drive member 5812includes internal threads 5850. The driven shaft 5814 includes anexternally threaded portion 5852. The externally threaded portion 5852mates with the internal threads 5850 to operationally couple the drivemember 5812 to the driven shaft 5814. That is, when the drive member5812 is rotated relative to the housing 5810 as indicated by arrow 5816,the driven shaft 5814 is prevented from rotating due to the linearprojection 5842 that fits within the linear recess 5840. As such,rotation of the drive member 5812 in the housing 5810 causes the drivenshaft 5814 to linearly slide 5818 along the linear recess 5840 due tothe engagement of the externally threaded portion 5852 mates with theinternal threads 5850. Since the outer shaft/tube 4910 is connected tothe driven shaft 5814 and the inner shaft/tube 4912 is connected to thehousing 5810, the outer shaft/tube 4910 is advanced and retractedrelative to the inner shaft/tube 4912 by rotation of the drive member5812.

In the example illustrated by FIGS. 58-61, the outer shaft/tube 4910 isfixedly connected in a recess 5850 in the driven shaft 5814 and anoptional seal 5852 is provided between the outer shaft/tube 4910 and theinner shaft/tube 4912 and/or between the outer shaft/tube 4910 and thedriven shaft 5814. A luer port 5862 is fixedly connected to the housing5810, e.g., a proximal end of the housing 5810 as shown. The innershaft/tube 4912 is fixedly connected in a recess 5860 in the luer port5862. The luer port 5862 is configured to accept a guide wire 5002 (SeeFIG. 49) that extends through the inner shaft/tube 4912.

In the example illustrated by FIG. 62-67, the handle 6200 includes ahousing 6210, a drive wheel 6212, and a driven member 6214. In theillustrated example, rotation of the drive wheel 6212 as indicated byarrow 6216 relative to the housing 6210 moves the driven member 6214linearly as indicated by arrow 6218 (compare the position of the drivenmember 6214 in FIGS. 64A and 64B). Referring to FIG. 62, the innersleeve/tube 4912 is fixedly connected to the housing 6210 and the outersleeve/tube 4910 is fixedly connected to the driven member 6214. Assuch, rotating the drive wheel 6212 in a first direction retracts theouter sleeve 4910 relative to the inner sleeve 4910 and rotating thedrive wheel 6212 in the opposite direction advances the outersleeve/tube 4910 relative to the inner sleeve/tube 4912. Although, inthe various embodiments shown in FIGS. 58-73, the inner sleeve/tube 4912is shown and described as being connected unmovably relative to thehandle or a proximal end of the handle while the outer sleeve/tube 4910is movable relative to the handle or a proximal end of the handle, inone embodiment using similar concepts, the inner sleeve/tube 4912 couldbe moveable relative to the handle or a proximal end of the handle whilethe outer sleeve/tube 4910 is connected unmovably relative to the handleor a proximal end of the handle, or both the inner sleeve/tube 4912 andouter sleeve/tube 4910 may be configured to be movable relative to eachother and relative to the handle or proximal end of the handle.

In the example illustrated by FIGS. 62-67, the housing rotatably acceptsan axle 6822 of the drive wheel 6212 to rotatably couple the drive wheelto the housing 6210. The drive wheel 6212 includes an engagement portion6230 that extends from the housing 6210 to allow a user to rotate thedrive wheel 6212 relative to the housing 6210.

In the example illustrated by FIGS. 62-67, the housing 6210 includes alinear projection 6240 (See FIG. 66). The driven member 6214 includes alinear groove 6242 (See FIGS. 62, 66) that the projection 6240 fitswithin to slideably couple the driven member 6214 to the housing 6210.

In the example illustrated by FIGS. 62-67, the drive member 6212includes a pinion gear 6250. The driven member 6214 includes a gear rackportion 6252. The pinion gear 6250 meshes with the gear rack portion6252 to operationally couple the drive wheel 6212 to the driven member6214. That is, when the drive wheel 6212 is rotated relative to thehousing 6210 as indicated by arrow 6216, the driven member 6214 slidesrelative to the housing 6210 due to the linear projection 6240 that fitswithin the linear recess 6242. As such, rotation of the drive member6212 relative to the housing 6210 causes the pinion gear 6250 to drivethe gear rack portion 6252 to cause the driven member 6214 to linearlyslide 6218 relative to the housing 6210. Since the outer shaft/tube 4910is connected to the driven member 6214 and the inner shaft/tube 4912 isconnected to the housing 5810, the outer shaft/tube 4910 is advanced andretracted relative to the inner shaft/tube 4912 by rotation of the drivewheel 6212.

In the example illustrated by FIGS. 62-67, the outer shaft/tube 4910 isfixedly connected in a support portion 6250 that extends from the gearrack portion 6252 of the driven member 6214 and an optional seal (notshown) is provided between the outer shaft/tube 4910 and the innershaft/tube 4912 and/or between the outer shaft/tube 4910 and the drivenmember 6214. A luer port 5862 is fixedly connected to the housing 6210,e.g., at a proximal end of the housing 6210. The inner shaft/tube 4912is fixedly connected in a recess 5860 in the luer port 5862. The luerport 5862 is configured to accept a guide wire 5002 (See FIG. 49) thatextends through the inner shaft/tube 4912.

Referring to FIG. 63, in one exemplary embodiment, the catheter 3600 maybe flushed by applying a fluid to the inner tube 4912, such as to theinner tube via the luer port 5862. As is described above, the deliverycatheter 3600 includes an outer lumen formed within an outer tube/sleeve4910 and an inner lumen formed within an inner tube/sleeve 4912, and theinner lumen and inner tube 4912 are longitudinally co-axial with theouter lumen and outer tube 4910. An annular lumen/gap/space 6348 inbetween the inner tube 4912 and outer tube 4910 that may result from,for example, the need to provide space for a crimped stent to travelthrough the catheter 3600. This gap/space 6348 can initially be filledwith air, which can be subsequently expelled and replaced with a liquid,e.g., a saline solution. Flushing in this way can be done with thevarious handle embodiments shown in FIGS. 58-73.

In one exemplary embodiment, a fluid such as saline or another suitablefluid, flows from the luer port 5862 and through the inner lumen ofinner tube 4912 as indicated by arrow 6360. In this embodiment, theinner tube 4912 is provided with one or more flushing apertures 6354.The fluid flows through the inside of the inner tube 4912, out theapertures 6354 as indicated by arrows 6370 and into the gap/space 6348.

As the gap/space 6348 fills with fluid, air is pushed out of thedelivery catheter through the distal end of the outer tube 4910. In oneexemplary embodiment, the nosecone 28 is disengaged from the distal endof the outer tube 4910 to allow the air to flow out of the outer tubeand out of the catheter 3600. Fluid also flows through the inner lumenof the inner tube 4912 to push air out of the inner lumen. In oneexemplary embodiment, the air is forced out of the inner lumen throughthe opening 6390 in the end of the nosecone 28 (See FIGS. 49A and 49B).This flushing procedure is performed before the delivery catheter 3600is introduced into the body. The device and method of this approachsaves space as compared to, for example, providing a side port on theouter tube 4910 for introducing a flushing fluid into the deliverycatheter assembly or gap/space 6348.

Referring to FIGS. 68-73, in one exemplary embodiment, the handle 6200illustrated by FIGS. 62-67 can be provided with a ratchet mechanism6800. The ratchet mechanism 6800 can take a wide variety of differentforms and can be used with the handle 6200 in a variety of differentways. In one exemplary embodiment, the ratchet mechanism 6800 is usedduring a “recapture” of the docking station 10 to pull it back into thedelivery catheter 3600. The force required to recapture the dockingstation can be significant. As such, the ratchet mechanism 6800 can beconfigured such that, when the ratchet mechanism is engaged (FIGS.68-71), the drive wheel 6212 can only be rotated in the direction thatdraws the docking station 10 back into the outer tube/sleeve 4910. Thatis, the spring force of the docking station 10 is prevented from pullingthe docking station back out of the outer tube by the ratchet mechanism6800. The operator can recapture the docking station 10 sequentially,without the docking station slipping back if the operator lets go of thedrive wheel 6212, for instance.

Referring to FIGS. 68-71, one exemplary ratchet system uses projections6810 with stop surfaces 6812 on one side of the projections and rampsurfaces 6814 on the other side of the projections. FIGS. 68-71illustrate an engaged condition where a ratchet arm 6892 is positionedto engage with the projections 6810 to permit the wheel drive wheel 6212to rotate in one direction, and to prevent the drive wheel from turningin the opposite direction. For example, the ratchet arm 6892 may beconfigured to ride over the ramped surfaces 6814 to allow movement ofthe drive wheel 6212 in the retracting direction 6850. For example, theratchet arm 6892 may flex to ride over the inclined ramped surfaces6814. The stop surfaces 6812 are configured to engage the ratchet arm6892 and prevent rotation of the drive wheel in the advancing direction6852. For example, the stop surfaces 6812 may be substantiallyorthogonal to a side surface 6870 of the drive wheel 6212 to prevent theratchet arm from moving over the projection 6810.

FIGS. 72 and 73 illustrate the ratchet mechanism 6800 with the ratchetarm 6892 moved out of engagement with the projections 6810. This allowsthe drive wheel 6212 to be turned in either direction. For example, theratchet mechanism 6800 may be placed in the disengaged condition toallow the drive wheel 6212 to be turned in either direction as thedocking station 10 is being deployed.

In ratchet systems, it is common to place the ratchet teeth on the outerperimeter of the wheel. By putting the teeth on the face of the wheel,the radial diameter of the wheel can be reduced, saving space. It alsoallows the outer perimeter of the wheel to be used as a grip for thethumb rather than, for example, having a second wheel for gripping thatis in engagement with a first wheel. The wheel itself is also allowed tobe thinner. The wheel may be made of any suitable material, such aspolycarbonate.

Referring to FIG. 71, in one embodiment the ratchet arm 6892 can be bentso that a portion of the arm can rest on a stabilizing bar 194 extendingfrom a housing wall or otherwise located within the housing, to preventthe arm 6892 from twisting as force from movement of the wheel isapplied to the arm.

The foregoing primarily describes embodiments of docking stations thatare self-expanding. But the docking stations and/or delivery devicesshown and described herein can be modified for delivery ofballoon-expandable and/or mechanically-expandable docking devices,within the scope of the present disclosure. That is to say, deliveringballoon-expandable and/or mechanically-expandable docking stations to animplantation location can be performed percutaneously using modifiedversions of the delivery devices of the present disclosure. In generalterms, this includes providing a transcatheter assembly that can includea delivery sheath and/or additional sheaths as described above. In thecase of balloon-expandable docking stations, the devices generallyfurther include a delivery catheter, a balloon catheter, and/or a guidewire. A delivery catheter used in a balloon-expandable type of deliverydevice can define a lumen within which the balloon catheter is received.The balloon catheter, in turn, defines a lumen within which the guidewire is slideably disposed. Further, the balloon catheter includes aballoon that is fluidly connected to an inflation source. With thedocking station mounted on the balloon, the transcatheter assembly isdelivered through a percutaneous opening in the patient via the deliverydevice. Once the docking station is properly positioned, the ballooncatheter is operated to inflate the balloon, thus transitioning thedocking station to an expanded arrangement.

In view of the many possible embodiments to which the principles of thedisclosed invention may be applied, it should be recognized that theillustrated embodiments are only preferred examples of the invention andshould not be taken as limiting the scope of the invention. Allcombinations or subcombinations of features of the foregoing exemplaryembodiments are contemplated by this application. The scope of theinvention is defined by the following claims. We therefore claim as ourinvention all that comes within the scope and spirit of these claims.

1. An expandable stent for implantation in a right ventricular outflowtract, the expandable stent comprising: a frame including: a waistportion that expands to a deployed size having a first diameter; a firstsealing portion extending from the waist portion and expanding radiallyoutward of the waist portion, wherein the first sealing portion is sizedto seal against a first portion of an inner surface of a rightventricular outflow tract at a deployed position over a range of sizesof expansion having a second diameter larger than the first diameter;and a second sealing portion extending from the waist portion in adirection opposite the first sealing portion and expanding radiallyoutward of the waist portion, wherein the second sealing portion issized to seal against a second portion of the inner surface of the rightventricular outflow tract at the deployed position over a range of sizesof expansion having a third diameter larger than the first diameter; anda band secured to the waist portion of the frame, the band restrictingexpansion of the waist portion substantially beyond the first diameter,such that the waist portion is configured to be spaced apart from theinner surface of the right ventricular outflow tract at the deployedposition.
 2. The expandable stent of claim 1, wherein the band comprisesa fabric.
 3. The expandable stent of claim 1, further comprising a firstretaining portion extending axially and radially outward from the firstsealing portion, the first retaining portion being configured to engagethe right ventricular outflow tract to retain the frame at the deployedposition.
 4. The expandable stent of claim 3, wherein the frame furthercomprises a second retaining portion extending axially and radiallyoutward from the second sealing portion, the second retaining portionsbeing configured to engage the right ventricular outflow tract to retainthe frame at the deployed position.
 5. The expandable stent of claim 1,wherein the band extends along an entire length of the waist portion. 6.The expandable stent of claim 1, further comprising a fabric coversecured to the frame along the waist portion, the first and secondsealing portions and the first retaining portion of the frame.
 7. Theexpandable stent of claim 1, wherein the frame comprises: a plurality ofstruts defining a center row of generally diamond-shaped cells, a firstend row of generally diamond-shaped cells extending to a first end ofthe frame, and a second end row of generally diamond-shaped cellsextending to a second end of the frame opposite the first end, each cellof the center row of generally diamond-shaped cells being positioned inend-to-end alignment with a corresponding cell of the first and secondend rows of generally diamond-shaped cells; wherein the center row ofgenerally diamond-shaped cells is expandable to a deployed size havingthe first diameter, the first end row of generally diamond-shaped cellsis expandable to the second diameter, and the second end row ofgenerally diamond-shaped cells is expandable radially outward to thethird diameter.
 8. The expandable stent of claim 1, wherein the firstdiameter is between 24 mm and 30 mm.
 9. The expandable stent of claim 1,wherein the band comprises a polyethylene terephthalate (PET) fabricextending along an entire length of the waist portion, the expandablestent further comprising a fabric cover sewed to the frame along thewaist portion and the first and second sealing portions of the frame,and wherein the first diameter is between 24 mm and 30 mm.
 10. A valveassembly for implantation in a right ventricular outflow tract, thevalve assembly comprising: a frame including: a waist portion thatexpands to a deployed size having a first diameter; a first sealingportion extending from the waist portion and expanding radially outwardof the waist portion, wherein the first sealing portion is sized to sealagainst a first portion of an inner surface of a right ventricularoutflow tract at a deployed position over a range of sizes of expansionhaving a second diameter larger than the first diameter; and a secondsealing portion extending from the waist portion in a direction oppositethe first sealing portion and expanding radially outward of the waistportion, wherein the second sealing portion is sized to seal against asecond portion of the inner surface of the right ventricular outflowtract at the deployed position over a range of sizes of expansion havinga third diameter larger than the first diameter; a band secured to thewaist portion of the frame, the band restricting expansion of the waistportion substantially beyond the first diameter, such that the waistportion is configured to be spaced apart from the inner surface of theright ventricular outflow tract at the deployed position; and aprosthetic valve secured with the frame in alignment with the waistportion.
 11. The valve assembly of claim 10, wherein the prostheticvalve comprises a plurality of leaflets sealingly secured with an innersurface of the band.
 12. The valve assembly of claim 10, wherein theprosthetic valve comprises an expandable valve frame expanded intoseating engagement with the band.
 13. The valve assembly of claim 10,wherein the band has a length equal to or longer than a length of theprosthetic valve.
 14. The valve assembly of claim 10, further comprisinga fabric cover secured to the frame along the waist portion, the firstand second sealing portions and the first retaining portion of theframe.
 15. The valve assembly of claim 10, wherein the first diameter isbetween 24 mm and 30 mm.
 16. The valve assembly of claim 10, wherein theframe further comprises a first retaining portion extending axially andradially outward from the first sealing portion, the first retainingportion being configured to engage the right ventricular outflow tractto retain the frame at the deployed position.
 17. The valve assembly ofclaim 10 wherein the frame comprises: a plurality of struts defining acenter row of generally diamond-shaped cells, a first end row ofgenerally diamond-shaped cells extending to a first end of the frame,and a second end row of generally diamond-shaped cells extending to asecond end of the frame opposite the first end, each cell of the centerrow of generally diamond-shaped cells being positioned in end-to-endalignment with a corresponding cell of the first and second end rows ofgenerally diamond-shaped cells; wherein the center row of generallydiamond-shaped cells is expandable to a deployed size having the firstdiameter, the first end row of generally diamond-shaped cells isexpandable to the second diameter, and the second end row of generallydiamond-shaped cells is expandable radially outward to the thirddiameter.
 18. A system comprising: a catheter including a sleeve; anexpandable stent for implantation in a right ventricular outflow tract,wherein the expandable stent is disposed in the sleeve, the expandablestent comprising: a frame including: a waist portion that expands to adeployed size having a first diameter; a first sealing portion extendingfrom the waist portion and expanding radially outward of the waistportion, wherein the first sealing portion is sized to seal against afirst portion of an inner surface of a right ventricular outflow tractat a deployed position over a range of sizes of expansion having asecond diameter larger than the first diameter; and a second sealingportion extending from the waist portion in a direction opposite thefirst sealing portion and expanding radially outward of the waistportion, wherein the second sealing portion is sized to seal against asecond portion of the inner surface of the right ventricular outflowtract at the deployed position over a range of sizes of expansion havinga third diameter larger than the first diameter; and a band secured tothe waist portion of the frame, the band restricting expansion of thewaist portion substantially beyond the first diameter, such that thewaist portion is configured to be spaced apart from the inner surface ofthe right ventricular outflow tract at the deployed position.
 19. Thesystem of claim 18, further comprising a first retaining portionextending axially and radially outward from the first sealing portion,the first retaining portion being configured to engage the rightventricular outflow tract to retain the frame at the deployed position.20. The system of claim 19, wherein the frame further comprises a secondretaining portion extending axially and radially outward from the secondsealing portion, the second retaining portions being configured toengage the right ventricular outflow tract to retain the frame at thedeployed position.
 21. The system of claim 18, further comprising afabric cover secured to the frame along the waist portion, the first andsecond sealing portions and the first retaining portion of the frame.22. The system of claim 18, wherein the frame comprises: a plurality ofstruts defining a center row of generally diamond-shaped cells, a firstend row of generally diamond-shaped cells extending to a first end ofthe frame, and a second end row of generally diamond-shaped cellsextending to a second end of the frame opposite the first end, each cellof the center row of generally diamond-shaped cells being positioned inend-to-end alignment with a corresponding cell of the first and secondend rows of generally diamond-shaped cells; wherein the center row ofgenerally diamond-shaped cells is expandable to a deployed size havingthe first diameter, the first end row of generally diamond-shaped cellsis expandable to the second diameter, and the second end row ofgenerally diamond-shaped cells is expandable radially outward to thethird diameter.
 23. The system of claim 18, wherein the band comprises apolyethylene terephthalate (PET) fabric extending along an entire lengthof the waist portion, the expandable stent further comprising a fabriccover sewed to the frame along the waist portion and the first andsecond sealing portions, and wherein the first diameter is between 24 mmand 30 mm.
 24. A system comprising: a catheter including a sleeve; anexpandable valve assembly for implantation in a right ventricularoutflow tract, wherein the expandable valve assembly is disposed in thesleeve, the expandable valve assembly comprising: a frame including: awaist portion that expands to a deployed size having a first diameter; afirst sealing portion extending from the waist portion and expandingradially outward of the waist portion, wherein the first sealing portionis sized to seal against a first portion of an inner surface of a rightventricular outflow tract at a deployed position over a range of sizesof expansion having a second diameter larger than the first diameter;and a second sealing portion extending from the waist portion in adirection opposite the first sealing portion and expanding radiallyoutward of the waist portion, wherein the second sealing portion issized to seal against a second portion of the inner surface of the rightventricular outflow tract at the deployed position over a range of sizesof expansion having a third diameter larger than the first diameter; aband secured to the waist portion of the frame, the band restrictingexpansion of the waist portion substantially beyond the first diameter,such that the waist portion is configured to be spaced apart from theinner surface of the right ventricular outflow tract at the deployedposition; and a prosthetic valve secured with the frame in alignmentwith the waist portion.
 25. The system of claim 24, wherein theprosthetic valve comprises a plurality of leaflets sealingly securedwith an inner surface of the band.
 26. The system of claim 24, whereinthe prosthetic valve comprises an expandable valve frame expanded intoseating engagement with the band.
 27. The system of claim 24, whereinthe band has a length equal to or longer than a length of the prostheticvalve.
 28. The system of claim 24, further comprising a fabric coversecured to the frame along the waist portion, the first and secondsealing portions and the first retaining portion of the frame.
 29. Thesystem of claim 24, further comprising a first retaining portionextending axially and radially outward from the first sealing portion,the first retaining portion being configured to engage the rightventricular outflow tract to retain the frame at the deployed position.30. The system of claim 24 wherein the frame comprises: a plurality ofstruts defining a center row of generally diamond-shaped cells, a firstend row of generally diamond-shaped cells extending to a first end ofthe frame, and a second end row of generally diamond-shaped cellsextending to a second end of the frame opposite the first end, each cellof the center row of generally diamond-shaped cells being positioned inend-to-end alignment with a corresponding cell of the first and secondend rows of generally diamond-shaped cells; wherein the center row ofgenerally diamond-shaped cells is expandable to a deployed size havingthe first diameter, the first end row of generally diamond-shaped cellsis expandable to the second diameter, and the second end row ofgenerally diamond-shaped cells is expandable radially outward to thethird diameter.